TWI356164B - Injector pump and device comprising the same - Google Patents

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an analytical device and a microarray having an integrated fluid inlet and outlet. The device is used for sample application and washing steps. More specifically, the present invention is an analytical device and microarray for integrating fluid inlet and outlet formed by a planar solid phase hydrophilic matrix loop containing dry chemical reagents, which can be used for medical diagnostics and other traces. analysis. [Prior Art] The prior art 'sidestream analysis device includes a microporous element that allows the sample to flow along the side, and a capture area for capturing the analyte in the sample. A lateral flow diagnostic device having a simple configuration comprising a rectangular porous strip that supports capillary flow over its length. In general, the use of the device for quantitative or sensitive detection is limited. Devices incorporating instruments that allow quantitative analysis of analytes in a sample have recently been disclosed. Lateral flow analysis strips have been commonly used in analytical techniques. The conventional lateral flow device in the simplest form consists of a rectangular porous strip that supports capillary flow over its length. One end of the analytical strip can be applied to detect an analyte in the sample, the analytical strip containing a first region of mobile reporter linkage (usually a visually observable reporter such as colloidal gold combined with a direct coupled analyte) An antibody) and a second region comprising a capture reagent (typically a second antibody that directly couples the analyte) and an outflow end. When the sample is provided by one end of the analysis strip, the analyte is combined with the reporter in the first region to form a complex; at this time, the sample contains a flowable analyte and the complex of the reporter flows to the second region and is captured. Reporters that are not combined with the analytes will flow to the end of the analysis bar and flow out on June 08, 100. The visually detectable signal in the capture zone quantifies the desired analyte in the zone. The above conventional lateral flow devices have been used in sandwich immunoassays as well as inhibition or competition binding assays. Because conventional lateral flow devices are inexpensive and quickly available, they are often used in non-laboratory applications, field testing (〇n_sitetesting), or medical diagnostic applications in the field. Conventional devices have also been used for non-device or non-quantitative medical diagnostics, and the concentration of the analyte can be predicted by the visibility signal of the capture region. However, conventional devices cannot be commonly used in quantitative analysis for two reasons. First, the visibility signal is more suitable for use in the analysis of the presence or absence of the quantitative analysis; secondly, the concentration of the complex with the reported gene and the combined amount of the capture zone are related to the flow rate. The diversity of device operation, especially the sample flow rate and sample evaporation, will have an effect on the signal to be detected. At present, quantitative side-flow devices have been disclosed in this field, which are used to measure the excitation light of the capture region with a laser when measuring the signal of the capture region or using the fluorescent reporter when using a chromophore reporter. Instrument. (U.S. Patent Nos. 5,753,517 and 6,497,842) U.S. Patent Nos. 5,753,517 and 6,194,222 disclose the method of measuring the amount of lateral flow of an instrument using internal control integrated into the flow path to internally correct different factors, especially corrections. Various different flow rates. However, even conventional quantitative flow devices do not meet the sensitivity or complexity of the laboratory. There are three main reasons for this device to cause low sensitivity: the first reason is the lack of a rigorous washing step, which can completely remove the reporter from the capture area without the analyte; the second reason is the lack of amplification step' The second reason is the lack of highly sensitive detection methods such as chemiluminescence measurements. Due to the lack of sensitivity, the lateral flow device was only used for general analysis with a large amount of analytes from June 8, 100 in the Republic of China. A small amount of analyte must still be analyzed using laboratory equipment with a rigorous washing step, amplification step, and chemiluminescence measurement technique. Conventional lateral flow devices have the disadvantages described above. U.S. Patent No. 6,306,642 discloses a device having a primary lateral flow element for forming and capturing an enzyme-conjugate/analyte complex and a complementary side comprising a chromophore matrix A flow element and means for delaying movement of the substrate in the capture zone. U.S. Patent No. 6,316,205 discloses a two-stage lateral flow device that is separated by a removable shield having a supplemental manual second stage cleaning fluid application when the sample is poured by using a lateral flow element. Absorb the pad to improve the washout of the unbound. The method of detecting analytes using a multi-step, high-sensitivity test in traditional laboratories has been known to the technique in 2002 by eds.  K.  Van Dyke, C.  Van Dyke and K.  Woodfork published a "Chemiluminescence Biotechnology" in the CRC journal containing a variety of high sensitivity luminescence test methods. An enzyme immunological kit based on a flow-through membrane capture structure (as opposed to a lateral flow pattern) has also been found in conventional techniques. This type of multi-step kit requires the addition of many reagents and a washing process, and is therefore not suitable for point-of care applications that require a simple single-step procedure. A single-step flow-through membrane immunoenzyme device is currently under development. U.S. Patent No. 5,783,401 discloses a multi-step enzyme immunoassay device for controlling a transport membrane to produce a time series reaction step. Devices containing electroosmotic extraction and compression to drive fluids in micropaths (capillaries, capillary channels or capillary paths) are well known in the art. These devices are commonly referred to as laboratory wafers (e.g., U.S. Patent Publication No. 4,908,112, issued on Jun. 08, 2005 and No. 5,180,480). Chemical reactions, mixture separation or analysis can occur by electrokinetic or compression of the microdevices in a fluid. However, in the prior art, the reagents are generally stored outside the wafer and are introduced when used. Moreover, such devices are generally used in the form of a continuous fluid type because it is difficult to construct a valve. A method of transporting a solid hydrophilic matrix using an electroosmotic method is disclosed in U.S. Patent Publication No. 20020179448. It is revealed by the electro-osmosis method that the number of turbulent years is 4 micro-twisting device #电ϋ装-骂则色美臀 patent disclosure No. 20030127333. U.S. Patent Publication No. 2, pp. A lateral flow immunochromatographic device using an electrochemical detection of an electrode is disclosed in U.S. Patent No. 6,478,938. In summary, the conventional single-step lateral flow diagnostic device lacks the quantitative amplification, washing, and high sensitivity detection steps. Conventional micropath devices have not integrated chemical substances and reagent storage devices in the micropath. This type of conventional technique is not as easy to use as a single step test and is inexpensive to manufacture&apos; but has a more advanced laboratory basis test for high sensitivity quantification, and such analytical methods are not affected by fluid composition and reaction vessels during operation. The present invention addresses the need to use standard lateral flow components and incorporates more advanced fluid components to mark conjugate, wash, amplify and enhance detection sensitivity without sacrificing speed, ease of use, and lower cost standard flow. technology. SUMMARY OF THE INVENTION The object of the present invention is to solve the problems of sensitivity and variability in the conventional single-step diagnostic technique described above, and to provide a more general single-step detection platform. Another object of the present invention is to provide a qualitative diagnostic test apparatus for a single-step quantitative diagnostic test and analysis test of the prior art of the present invention. It is also an object of the present invention to provide a syringe pump that controls the suction of fluid to reach a receiving area of a fluid receiving element, more preferably a lateral flow path component of a diagnostic test device. In a preferred embodiment, the syringe pump includes a fluid path that is initially dry, preferably microporous, having a fluid application end for receiving fluid and an effluent end. To the use side. Preferably, the syringe pump further includes a drive means for electrically venting the fluid from the outflow end of the fluid path and past the separator. Preferably, the drive means is a pair of spaced apart first and second electrodes for generating an electric field to drive the fluid through the fluid path after passing through the wet separation element. In another preferred embodiment, the syringe pump further includes an integrated separation element to isolate the outflow end of the fluid path from the fluid receiving area; preferably the separating element or separator is an air gap to prevent capillary flow through Outflow end. In a syringe pump with air spacing, when the microporous fluid path has a surface charge and a zeta potential, the potential difference can electrically permeate the fluid through the air space. Preferably, the first electrode is in contact with the fluid in a first region of the fluid path and the second electrode is in a second, separate region for electrical contact with the fluid at the use end. When using an integrated diagnostic device with a syringe pump, fluid is supplied to the fluid use end of the fluid path of the pump (sample fluid or fluid preferably stored in the integrated reservoir, when used by the device This is shipped to the use side). The fluid fills the entire fluid path by the sidestream capillary from the first fluid use end to the second outflow end. A voltage is transmitted to the two separate zones. The electricity is permeated through the fluid path. The substance of the matter is related to the injection of a reagent such as a flowable reagent bound to the side along the length of the microporous fluid path. The chemical f can be a reporter complex, for example in a sample. Injecting two of them can react with the analyte or can be used as a wash or enzyme. The chemical in the fluid path can be moved to the use end of the path and the fluid can be drawn to the lateral flow device under the condition of controlling the flow device. Preferably, the electro-optic, chemically-emitting substrate is a cold-powered m. A further object of the present invention is to provide a microtesting device that incorporates a syringe pump of the present invention. The syringe pump can be used to control fluid flow into other fluid paths and provide for the addition, washing and amplification steps of at least one of the chemical reactions in the device. Another object of the present invention is to provide a microanalytical device that incorporates fluid components, thereby providing more advanced fluid handling. The fluid element includes a lateral flow element that supports the disrupted capillary fluid and an element that is driven by the electroosmotic side flow. The invention may have any number of the above two fluid elements, as long as one element is used for the sample and at least one element is part of the syringe pump. Another object of the present invention is to provide an analytical device (e.g., a reporter complex or an enzyme substrate) having a fluid element with an integrated chemical. The integrated chemical can be applied to move the fluid to the component. If the applied fluid is a sample and the moving chemical is a reporter complex, the chemical can be combined with the analyte or shipped to the chemical. Other microreaction zones of the component. When the chemical substance integrated with the fluid element is an enzyme substrate, the substrate can be a luminescent, fluorescent, luminescent, power generating substrate. There are also 11 1356164 Republic of China on June 08, 100. It is possible to integrate non-enzymatic markers into fluid components. A further object of the present invention is to provide a single integrated diagnostic assay device with some or all of the reaction chemistry, as well as to perform a solution-based chemical reaction, such as analyte calibration, capture, post-capture wash steps, amplification, and High sensitivity to detect the required fluid. One object of the present invention is to disclose how to fabricate the device in a microfabrication process. The pre-measurement method depends on whether the chemical is selected for use in a syringe pump or integrated with fluid components. The present invention further discloses that an integrated diagnostic device can be used to generate signals and be detected and quantified by an external device. The device can also be produced in the form of a diagnostic card containing electrodes that can be inserted into an external device. The external device can also provide the power requirement to control the movement of the fluid from one or more fluid components to the microreactor in the device. An external device can also be connected to the diagnostic card and detect the reaction that occurs on the microreactor. In the preferred embodiment, the injector pump is an injury to the microtest device that can be used to control fluid entry into other micropaths in the device and to provide reagent addition, washing and amplification steps in the chemical reaction in the device. The pump is also used for the second fluid path. Another preferred embodiment is a diagnostic device comprising a syringe pump and a lateral flow element having a capture zone for binding sample molecules to the analyte molecules. This syringe pump provides the power needed to wire, bond the marking application, and amplify and capture the composite. (4) The component (4) has a sample application end and a micro reaction area. In the single-step operating device of the present invention, a user introduces a sample into the diagnostic device&apos; and connects the diagnostic device to an external connection control device. The sample fluid is any chemical or biological stream containing the analyte. Sample flow 12 1356164 The body of the Republic of China flows through the capillary side of the fluid element to the micro-reaction area, after which the other reaction liquid and washing liquid will Under the control of the instrument, it is introduced into the microreactor area and flows through other integrated fluid elements containing reagents under the time-interval sequence. The final device still retains the simplicity of the conventional lateral flow device because it requires only a single step (other steps are automatically operated by the machine) and is inexpensive, but enables quantitative analysis of low levels of analyte. The apparatus of the present invention can be configured in a number of different fluid arrangements and is tested in accordance with the "-+m"-two in the preferred embodiment of the present nf. In the first test, a combination is first bound to the analyte in the sample fluid to form a complex, and then the complex of the analyte and the conjugate is captured and detected by the detector, captured. The amount of complex is proportional to the concentration of the analyte in the sample. In the second experiment, the analyte is captured first, and then the captured analyte is reacted with the k s conjugate and tested. In a preferred embodiment of a test device, the invention is directly applicable to a ligand binding assay in a sandwich format that binds to the analyte prior to being captured. The integrated instrument control fluid device of the device comprises a first microporous flow element for fluid passage and at least one other microporous flow path for providing other fluids to enter the fluid storage tank of the first side flow element under instrument control. . The first side flow storage tank has a first end for sample use and a second outflow end. A selective sample application pad and a selective reagent application are contacted with the sample application end of the first lateral flow element, and the selective fluid collection potential is in contact with the outflow end. The first side flow element will be in contact with the flowable dry reagent. For example, when performing a sandwich-type ligand binding test, the flowable reagent of the first side element (or the reagent 与 in contact with the fluid) may be a reagent-binding reagent (immunoassay-imposed antibody or 13 1356164). The conjugate of the nucleic acid in the nucleic acid test on June 08, 100, with a label or reporter molecule (eg, the first porous element of the enzyme reporter has a reaction zone in the microreactor. The first microwell The reaction region of the element may be, for example, a capture region containing an immobile second binding agent (a second antibody in the immunoassay that binds to the analyte or a second nucleic acid in the nucleic acid assay). The first microporous fluid path element may A second fluid path is connected to the fluid receiving area to inject the first tear body, and the second fluid path is actively controlled by the instrument and is mostly injured by the main lens. The first fluid path is used for one purpose. Microporous elements for the first end and the second outflow of fluid applications. Initially dry and flowable dry reagents (eg, for enzyme labeling in ligand binding assays) An air gap separates the outflow end of the second path from the fluid receiving area of the first side flow element, which constructs a separate device. When the apparatus is used, the sample fluid is added to the first first side stream 70 that is initially dry. Another low conductivity electrolyte fluid, typically preferably stored in a male, sealed storage tank integrated into the device, is introduced into the initially dried second fluid element from the fluid use end. Controlling injection from the second fluid path The instrument device to the first lateral flow element is driven by electroosmosis generated by the surface pores of the second fluid path of the micropores having surface charge and interface potential. The preferred way to provide electrical drive to the second fluid path is to use Integrated electrode. The preferred electrical contact between the integrated electrode and the second fluid path is to have a free field (10)d at the outflow end of the path. When the instrument controls the power of the pump to provide a second fluid path, the fluid contains a flowable reagent, - a fluid-reading microreactor that reacts a fluid with a fluid and a reagent contained in an example of a sandwich labeled with an enzyme as t, a second fluid The enzyme substrate provided by the path will contain the enzyme labeling reaction of the first fluid element of the fish. The reaction can be detected. 14 1356164 The Republic of China 100 years, June 08. The detector close to the microreactor will measure the microreaction The concentration of the analyte in the sample fluid produced by the reaction in the device. Some highly sensitive detection methods in the prior art can be used in the present invention. The enzyme substrate controlled by the instrument to be injected into the microreactor can have Luminescent, fluorescent or chromogenic properties. A luminescent substrate reacts with an enzyme to emit a light signal, a fluorescent substrate also emits radiant light, and a chromonic substrate reacts to produce an absorption or reflection spectrum of the incident light. Change. In these cases, try to use the H (proximal detector) ϋ H to be a light detector. If you use a substrate that produces an electron with the enzyme, the near-side detector is best used. An integrated electrochemical detection electrode in contact with the microreactor region. It is also possible to use non-enzymatic labels such as the well-known chemiluminescent acridinium esters. In this example, the reagents controlled by the instrument for injection into the microreactor region are known chemiluminescence trigger reagents and the use of photodetectors to detect reaction products is preferred. The preferred detection mode of the present invention is a luminescent light and photodamper. When the enzyme label uses cold light as the detection method, it is best to use alkaline phosphatase. In this case, 'high sensitivity cold light acceptor such as dioxin (such as adamantyl methoxybenzene) can be used. Adamantyl methoxy phenyl phosphate dioxetanes &gt; AMPPD). Another well-known high-sensitivity alkaline phosphatase matrix is luciferin-ortho-phosphate, which is compatible with luciferin, adenosine triphosphate (ATP), and money. The ions are supplied together to the capture area. In this case, the luciferin acid salt is decomposed by luciferase by a test enzyme, and it is converted into bioluminescence by the action of luciferase. It is also possible to use lactose-degrading enzyme labeling with its amantadine 15 1356164. The amanatine-dioxetane luminogenic substance was developed on June 08, 1995. Another well-known high-sensitivity test uses ethyl ester kinase (acetate). In the case of the calibration, in this case, the substrate will provide acetamidine phosphate, diammonium (ADP), luciferase, and magnesium ions to the capture zone. In this case, ethyl ester kinase catalyzes the production of adenosine triphosphate (ATP), which can be detected by bioluminescent reactions. In another example, the enzyme label can use a conventional horseradish peroxidase to enhance the action of the sensitizer. When the enzyme label is used for fluorescence detection, the enzyme is preferably alkaline ligase and high sensitivity fluorescent matrix methyl umbiferyl phosphate (MUBP). When the enzyme label is used in the electrochemical detection mode, it is preferable to use an experimental acidase and para amino phenyl phosphate as an electronogenic substance. A preferred embodiment of a diagnostic device is a ligand-binding microtest device in which the labeled binding complex will produce a complex with the analyte in the sample. The complexes produced by the analyte and the complex are captured and measured, and the amount of the captured complex is proportional to the concentration of the analyte in the sample. The first side flow element is a flowable reagent with a combination of enzyme labels. As the sample fluid flows through the first lateral flow element, the enzyme labeled binder will bind to the analyte in the sample. A captured complex comprises an enzyme-labeled analyte formed in a microreaction zone in a first fluid element, the sample fluid comprising a complex comprising an enzyme-labeled analyte traversing the microreaction zone and immobilized to the capture site Produced when the binding reagent is combined. The flowable reagent contains the enzyme in the second flow path and is transported to the outflow end when it is filled with capillary flow. The isolation method ensures that the fluid and flowable agent of the second fluid path are separated from the first lateral flow element prior to being injected into the first flow element and are controlled by the instrument to enter the reactor zone of the first flow element. In the sandwich-type ligand binding test set 16 1356164 in the Republic of China on June 08, the instrument control fluid injection into the second fluid path was driven by electro-osmosis. The surface of the micropores in a fluid path has surface charge and interface potential. When the instrument controls the power of the pump to the second fluid path, the fluid, which contains the flowable reagent, is injected into the storage region of the first lateral flow element. The fluid is transported to the first microreactor to interact with the fluids and reagents therein. Next, the instrument-controlled pump power will again provide the second fluid path and the fluid in the first micro-reactor will be sent to the second micro-reactor and the test-remaining--" The value Jgij-qin measures the concentration of the analyte in the sample stream produced by the second reactor ten. A two-stage reaction using an enzyme substrate such as luciferin orthophosphate can be applied to the above apparatus. Luciferin orthophosphate is added to the first lateral flow microreactor zone containing the alkaline phosphatase labeled capture complex. After the reaction period (incubati〇n step), the product of the reaction, luciferin, is transported in an instrument-controlled fluid to a second microreaction zone with luciferase, triadexin or other reagents and produces organisms. Fluorescent signal. The other two possible two-stage reactions use ethyl ester kinase calibration with triethylphosphoric acid phosphate, glyphosate diphosphate, and magnesium ions to produce triadenin in the first reaction phase. The triglycine will flow to the second microreaction zone with luciferase and luciferin to produce a bioluminescent signal. In another embodiment of the invention, the analyte is directly captured after labeling, and the apparatus preferably comprises a first microporous lateral flow element having a sample fluid use end and an outflow end, a capture zone. The volume of this element is equal to the volume of the fluid. The device further includes an auxiliary fluid path component that can be actively and independently extracted under instrument control. The auxiliary fluid path includes microporous elements including the use end and the outflow end of the sample. Each microporous element has a surface charge and an interface potential and is in contact with an integrated electrode that provides instrument control power to drive electroosmosis. With each of the 17 Republics, 100 years, June 〇 8 曰 auxiliary fluid path better electronic technology ^% thousand contact position is the zero field of the outflow end (five) dfreereglQn). Each of the auxiliary fluid paths 1 is initially dry and optionally contains a flowable dry reagent. Each of the auxiliary fluid paths has an air barrier that separates the outflow end from each of the three fluid receiving regions in the first-side flow element. Sister Demon Team When using the device, the sample fluid is applied to the initially low:! flow element. The second fluid is a low conductivity fluid solution, preferably stored in a sealed "body storage; ff' the fluid will be introduced into each of the initially auxiliary fluid path elements. The sample fluid is pushed by the capillary fluid through the first - In the lateral flow, the second fluid will fill each of the auxiliary fluid path elements, thereby transporting the reagent to the outflow end. The air isolation is to ensure fluid in the auxiliary fluid path and fluid in the first-side flow element And the reagent is separated until the instrument controls it to be injected into the first-side flow element, and then the instrument uses the osmotic pressure to control the fluid to propel the fluid to the first fluid element. When the machine controls the power of the pump to provide the auxiliary fluid path, the fluid, including The flowable reagent is injected into the first fluid element. In another embodiment of the apparatus, there are three active auxiliary suction fluid paths. The first one provides a combination of enzyme markers, the second provides a wash solution, and the second provides the enzyme substrate required for the capture area of the first fluid element. In this embodiment, the sample fluid is injected into the originally dried application end of the first lateral flow element and then flows to the outflow end by capillary action in the tube. The analyte to be dissolved in the fluid is analyzed along the capture zone of the lateral flow element. The volume of fluid flowing through the capture zone is known because the volume of fluid filled with the component is known and is controlled by the volume of the downstream component of the capture zone. The next step &apos; first injection fluid containing the enzyme labeled combination flows from the first auxiliary fluid path to the first lateral flow element of the first injection zone. 18th June, 100, 100. An injection fluid flows from the first lateral flow element to the outflow end as it flows to the service end. In this step, the sample fluid in the first-side flow element is flushed out and replaced by the first injection fluid. The first injection enters the capture zone and forms a sandwich complex when the labeled complex binds to the analyte of the capture zone. Next, the second wash liquid is injected into the second auxiliary fluid path into the first side stream element of the second injection zone. The second fluid flows through the first lateral flow path to the outflow end. In this step, the first injection fluid of the first lateral flow element is shrunk and removed - the capture - the data - the I domain - the - he - not I will be established as a body - and the cover is covered by the watch - The liquid is replaced by one. Importantly, the first injection fluid containing other excess unbonded junctions must be flushed out as much as possible to remove unbonded markings. Next, a third injection containing an enzyme substrate under the control of the instrument is injected into the first lateral flow element of the third injection zone by a third auxiliary element. The third fluid is from the first side &quot;丨L pathway/)丨L to the outflow end as flowing into the injection end. When the third injection containing the enzyme is flowing to the capture area, the instrument controls the injection to stop. At this point, the enzyme is bound to interact with the enzyme-labeled complex. 5 The reaction detected by the Xuan reaction is proportional to the concentration of the captured complex, and the concentration of the complex is proportional to the concentration of the analyte in the sample. This signal will be detected by the detector near the capture area device. Alternatively, the selective attack is a washing step prior to injection of the conjugate (washing the sample fluid from the reaction zone), and the instrument controls the stripping action after the injection of the human body. Any of the above high sensitivity detection methods can be used on the device. There are many other fluid devices and test methods that can be considered for use in the aforementioned devices. In general, the integrated diagnostic device of the present invention comprises at least one substrate (or a multiplexed microreactor array) having a signal generating microreactor, an integrated reagent, and a fluid. A microreactor contains a container that can hold aqueous chemistry 1356164 Republic of China on June 08, 100. The chemical reaction produces a detectable signal that determines the concentration of the analyte in the sample fluid. The microreactor can further comprise a selective capture zone. Each microreactor has an integrated fluid comprising a network of N fluid influx pathway elements and helium fluid outflow pathway elements. The fluid path is an element that is driven by capillary phenomena. A fluid path has a fluid inlet end and a fluid outlet end that allow fluid to flow into and out of the element. The helium fluid influx pathway and the helium fluid outflow pathway are initially dry components, which, when used, are filled with side capillary flow when the fluid is added. In a microreactor array, each microreactor will be connected to a fluid network, and the number of helium fluid inlet elements and helium fluid outflow elements may vary from one microreactor to each microreactor. Using this diagnostic device, some or all of the initially dry helium and helium fluid paths are filled with fluid by side capillary flow. At least one of the sputum and sputum routes is a syringe. A syringe is defined as a fluid path element that can be actively pumped by the instrument. After the fluid use end to the outflow end is filled with capillary flow, the outflow end is separated from the other fluid elements (such as other fluid paths and microreactors) by air separation. The fluid does not exceed the outflow end, and the reagents in the path do not react with other pathways or chemicals in the microreactor until the fluid in the fluid path of the syringe is actively sent out of the outflow to the other fluid element. The helium fluid path itself may be the active snorkeling member, that is, 'actively controlled by the machine but not the syringe element. Because it is actively absorbed without fluid isolation, the non-injector element, the fluid flowing out of the fluid-filled component will The instrument is used to control the power of the pump. It is in contact with other fluid path components because there is no isolation device. Other W Μ fluid paths can also be passive pump components. 'The pump is not controlled by the instrument to actively draw fluid, but can be taken from the outflow end. The wick effect device (wickmg knows - non-instrument control method passively draws. There are still other ways not to pump components. These elements 20 1356164 Republic of China 100 years June 08 when the pieces are full of fluids will not move until the second is given The pressure causes the drive fluid to move. Some 1 and M fluid paths can also contain microporous sidestream materials, or a traditional flow of empty pipes or pipes. Body composition. The active pumping path element is an electro-osmotic method, and the pump path 7C has at least one charged capillary surface area and an interface potential. The active suction power is controlled by the instrument, preferably separated by a pair. The integrated electrode is provided, at least one of which will be in contact with the fluid path of the pump, and the other one of the other areas - the n-contact is in contact with the fluid of the rabbit body. The dry fluid path element may contain a dry reagent that can be moved by the aqueous fluid introduced by capillary flow. If the path 70 is an active suction element, the movable reagent can be transported to another location under the control of the instrument. In particular to the microreactor. Any or all of the paths may contain a capture reagent that captures and immobilizes the chemical in the fluid. In the above general embodiment, at least one of the initially dried N fluid injection paths is filled with the sample by capillary flow. Some or all of the other initial drying paths may be driven by capillary flow or other aqueous fluids. When the device is in use, 'when the fluid is not a sample liquid', the path is preferably initially provided and filled with at least one integrated fluid in the sealed storage tank. The microreactor system of the various embodiments of the invention. It is a reaction tank structure. A reaction tank structure breaks the contents of the reaction tank in a fixed position during the reaction. A microreactor may be a microporous flow path element or a chamber or pipe connected to the fluid path element. The chamber or pipe may be locked or in communication with atmospheric pressure. A signal generates a microreactor region to produce a reaction. 21 1356164 The signal of the birth of the Republic of China on June 08 is proportional to the concentration of the analyte to be detected. The signal-generating microreactor is positioned adjacent to the detector that monitors the reaction during the reaction. In a preferred embodiment of the invention, the ligand binding assay is applied to the side of the microreactor region containing the capture century. Flow component. One of the preferred embodiments' microreactor is a microporous fluid path component region having an open top reaction chamber. It comprises a plate member having a microporous fluid path surface filled with holes. The plate holes are located in the fluid path reaction region. The sidewalls of the plate aperture form microreactive grooves, and the planar substrate of the reaction zone of the first fluid path component forms the base of the microreactor. At least one of the syringes is located at the edge of the recess and fluid is actively drawn into the recess and flows directly to the first fluid path component. When the fluid fills the container recess of the microreactor, air escapes through the top cover. In another embodiment of the chamber exhaust reaction, the outflow end of at least one of the injectors is located at an outer side edge of the recess. In still another embodiment, the microreactor is a closed chamber or conduit interposed in the reaction zone of the microporous fluid path. The cross chamber or pipe system can be blocked or discharged.  pressure. In yet another embodiment, the microreactor is a region of a microporous fluid path component and the fluid is completely sealed to the edge. There are areas where many electrons may come into contact. In one case, the contact location is two separate spaces in the path. The first zero field region is located between the first fluid use end and the first contact region, and the second zero field region is located between the second contact region and the path outflow end. In another case, the first electronic contact area is located at the first use end of the path (or electronic contact outside the path of the first use end), and the second electronic contact is located on the path, at the use end and the second contact area. There is an electronic field between them, and there is a zero field between the second contact end and the outflow end. In some less desirable cases, the electronic contact is at the bottom of the component. In this case, there is a fluid filled with the entire piece in the electronic field. 22 Weeping The 100-year-old 〇November 08 outflow end preferably has zero field space. In the middle of the slaughter: When the path of the initial dry phase contains a dry reagent that can be circulated, the dry soldering agent can be placed in the dry path of any t λ dry during the outflow end of the device, when the product is added. 2. When the syringe is used in the zero field, the first fluid in the path of the first drying path is transported to the outflow end of the path and == the reagent will pass through the device. When electric is applied to the end. In i, the flow of fluid containing flowable reagents will be sent out and out - class one 1 &quot; Europe, (four) Tonglan often zero field area. Here - there is no negative effect (power does not generate electricity and does not produce an electrochemical reaction at the electrode). And the electro-osmotic pump must be able to propel the fluid at a useful speed, and the rain is strong. If the hitting person (10)f passes the resistance factor, it resists the equivalent back pressure (the typical reflow fluid resistance of the present invention, the help flow out The end pressure is about - atmospheric pressure or higher. In order to achieve this requirement, the pumping part of f (between the electronic contact parts) must be microporous and must have a potential of 4 solid microporous fluid paths with a pore size of less than one micron, preferably less than G. 2 microns. For riding efficiency and reproducibility, the microporous electroosmotic pump area needs to be sealed around. - surrounding unsealed pump components, since the microporous plate contains ambient air (as is conventionally arranged for lateral flow components), it is not resistant to back pressure to produce efficient suction because it is opposite to the path and the outflow end The direction of the fluid is removed by the holes in the plate. There are two ways to distribute the injection to the fluid receiving element. In both ways, the outflow end of the syringe is separated from the fluid receiving element of the other fluid element by air spacing. In the first configuration, the outflow end of the syringe, the gas gap and the fluid receiving area of the other fluid element are sealed in a chamber containing air. The air chamber does not escape into the outside atmosphere. Syringe 23 1356164 June 08, 100 The fluid receiving element is initially filled with fluid. When the syringe is charged, the fluid therein will flow from the outflow end to replace the air in the isolated region of the closed chamber so that the fluid can contact the receiving region of the fluid receiving member. The air in the sealed chamber is pressurized and pushes the fluid in the syringe into the fluid receiving element. When the pump is turned off, the compressed air pushes the fluid into the fluid-receiving element' and returns the air to the position of the air that was originally located between the outflow end of the syringe and the fluid-receiving element. This process is accelerated by operating the reverse polarity of the syringe pump, allowing fluid extraction in the chamber to be faster. After this process, the syringe is in a stopped state and is again separated (electrically or fluidly) from the fluid receiving element. This method allows multiple syringes to be used along the sample fluid element, which is isolated when closed and fluidly connected when opened. This method can use multiple independent pump-driven syringes in sequence without interfering with the use of the pump (if it is permanently connected to the fluid with power). Furthermore, a syringe can draw fluid under the control of the instrument, and when the other fluid device performs the same action, it stops and then restarts. In the second configuration, the sealed air chamber is controlled by a path air valve to escape the outside air. When the injector is powered, its fluid is forced out of the outlet to replace the air in the air isolation region outside the enclosed chamber so that the injection fluid can contact the receiving region of the fluid receiving member. The gas chamber still maintains a general atmospheric pressure, and the injected fluid is not pushed by the compressed air to the fluid receiving element. The reagent in the injected fluid contacts the fluid receiving member to diffuse to the receiving member and react. In the present configuration, when the injection step is operated, the fluid that is ejected when the reverse pole power is applied can be pulled back thereby separating the pump from the fluid receiving element. The air separation at the outflow end of the fluid path of a syringe is a fluid barrier method. The gas spacing region is __ the space is located between the syringe fluid path and the flow rate between the end and the other fluid receiving element. When the fluid is added to the fluid use end of the fluid path of the initial drying of the syringe, the fluid is filled by the capillary flow to the outflow end and stops at the air gap. This isolation effectively prevents the capillary flow from exceeding the outflow end of the fluid path. When the syringe fluid path fluid resistance (maximum when the aperture small fluid path is long) is large enough, the stopped syringe fluid is prevented from leaking to the outflow end of the syringe path, even at the input and outflow of the syringe path when using the diagnostic device The end of the meeting may be ... will be 4 - raw J pressure: force, offering equipment to avoid capillary - the power of color absorption will be caused by the other fluid components on the surface of the path of the input and outflow end. The air gap is preferably sized to prevent any fluid from accidentally leaking out of the syringe without escaping the air gap to cause fluid isolation. ♦ When the syringe is activated, the voltage is applied to a fluid-filled syringe with an area containing surface charge and interface potential; the fluid moves to the gas-insulated area and out of the fluid-receiving element. The syringe must be able to draw at a useful rate (as required by the test) to overcome the back pressure caused by the fluid resistance of the fluid receiving element, while the air isolation device needs to be sized to allow the injection fluid to pass at an effective time. The fluid receiving element is an element that connects the outflow end of the syringe. Perhaps it is a microporous pathway or a gas chamber component or a conventional open conduit, conduit, chamber°. = The body receiving element can be dry initially or received by a syringe: = filled for it. When the fluid of the syringe is received ‘If the fluid receiving element is microporous and dry, the received fluid will flow due to the action of the capillary wick. If the fluid receiving element is already filled with fluid when it is received by the syringe, the received fluid replaces the existing fluid when the fluid receiving area of the receiving element is connected to the syringe that locks the air chamber. The fluid-receiving element can have an interface potential and is connected to the integrated electrode to receive the fluid and further electro-permeate. 25 1356164 The Republic of China, June 8, 100 pushes or injects another connected receiving element. A microporous fluid path system can contain a variety of different materials. This type of material has a hydrophilic surface that produces a capillary wick for the aqueous solution. For example, cellulosic cellulose, cellulate nitrate, polyethersulfone, nylon, polyethylene, and the like can be used. The microporous fluid path of the syringe pump can be a single element or a combination of more than one element through which fluid flows by capillary action. The microporous electroosmotic injection element may further comprise a material having surface charge and interface potential, and cellulate nitrate is a preferred material. The sealing member used in the present invention is an electrically insulating material capable of producing a sealing effect at the edge of the fluid path member. The sealing element used in the syringe of the present invention can be any pressure sensitive colloidal component known to date, such as siloxane, acrylic glues. This type of material forms a seal by applying pressure when a sheet is formed around the syringe. Many other insulating sealing materials can be used as the insulating protective film in the device of the present invention. Diagnostic devices with integrated device control fluids are available in two manufacturing styles. In the first mode, the microporous fluid path elements are formed from a membrane, such as by die cutting, and then combined and sealed onto a planar substrate. In the second method, the fluid path component is produced by a sheet micromachining process. In this technique, each of the microporous materials is produced by a precipitation technique such as spin coating on a planar substrate, and a phase transition is formed by the film material dissolved in the solution during the spin drying of the spin coating. The phase change material is microporous. The final microporous dried sheet can be formed into the fluid path by photographic printing, which includes photoresist coating, exposure, patterning of the photoresist, and application of the gaseous plasma to the metal. Move 26 1356164 The Republic of China on June 08, 100 to the microporous membrane. Micromachined materials, methods of forming microporous fluid path components, and edge seals are described in more detail in U.S. Patent Publication No. 2, 127, 333. The dry reagent contained in a particular location of the microporous fluid path element can be precipitated using a nozzle micro-dispensing step known in the art and is often used in the manufacture of lateral flow element devices. Other membrane-based dry reagent devices. Other embodiments of the present invention comprise an array of detection devices comprising an array of a Xixia microreactors made of --------m-r m. In a preferred embodiment of the array device, it is fabricated by micromachining techniques. Other aspects and features of the present invention will become apparent to those skilled in the <RTIgt; [Embodiment]

BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 is a diagram showing a portion of an instrumentation electroosmotic syringe of a diagnostic apparatus of the present invention. The syringe and injector pump are replaceable throughout the detailed description. Fluid paths, fluid components, and fluid path elements are also replaceable. The separation element, the separator, the fluid receiving area, and the fluid receiving position can also be replaced. The first figure is a top view showing a substrate having two integrated electrodes that are in electrical contact with the initially dried microporous fluid path component. The first electrode has a contact pad 7 for connecting electronic circuitry, and the contact area 8 can make electrical contact with the fluid element i. The second electrode has a contact pad 5 for connecting the peripheral circuit, and - a contact area 6 adjacent to the fluid application end 2 of the fluid element 1 for providing electrical contact with the body from the fluid application end 2, the first sealing element 9 In the fluid of the syringe, 70 pieces 1 and the fluid receiving area 13 cover the substrate 1〇, but do not cover the electricity. 4 27 1356164 The contact area of the Republic of China on June 08, 5, 6, 7 and 8» The second sealing element covers the fluid path element of the injector but does not cover its fluid application end 2 or its outflow end 3»the second sealing element also covers a portion of the receiving element ι2 but does not cover its fluid receiving area 13. The first and second sealing members 9, 11 form a sealing sheet around the syringe, as shown in the first c-figure, which is a cross-sectional view taken along line B_B of the first A drawing. Here, a covering member 23 is located on the sealing member 11 of the outflow end 3 of the syringe and the receiving region 13 and the opening of the fluid receiving member 12. The cover member 22 is post-sealed to form a latching gas 15 around the second sealing member 11 at the outflow end 3 of the syringe and the receiving region 13 of the fluid receiving member 12. Here, an air insulating member 14 fluidly blocks the outflow end 3 of the syringe and the fluid receiving region 13 of the fluid receiving member 12. The fluid receiving member is a microporous strip having one end connected to the fluid circuit 21 and the other end connected to the fluid circuit 2 2 ' to constitute the same fluid application region. A fluid injection zone 13 is provided along its length. The same fluid is applied to the sample fluid application area of the fluid circuit 22 during use of the device containing the injector. An electrical connection is made via contact pads 5 and 7 with an external electronic control circuit. A fluid is introduced into the fluid application end 20 of the apparatus to make electrical contact at the contact area 6 of the electrode and to make fluid and electrical contact at the fluid application end 2 of the fluid path element 1. The fluid flows to the element 1 by the capillary wick phenomenon, filling its outflow end 3 but not exceeding it. During this time, the fluid in the syringe will be separated from the fluid receiving element 12 and other fluid circuits connected thereto by the air insulating member 14, such as the regions 21, 22 shown in Fig. a. Instrument control power is applied to the electrodes. - the voltage difference between the power electrode of the contact region 8 and the grounded electrode of the contact region 6 is generated between the contact regions 6 and 8 of the length of the fluid element 28, June 8, 100, Republic of China -electric field. When the micropores of element 1 have an interface potential, the electric field drives the electroosmotic fluid. When the table = 3⁄4 load and the interface potential is negative &amp; 'the negative voltage of the contact area of the position 8, the weeping body 1 is pushed by the fluid application area 2〇 through the fluid path of the syringe and flows out: = 3 ° spare fluid outflow and outflow The end 'will replace the air isolation 14 to the end 15 of the element 16 of the lock chamber U and compress it. Now that the fluid is in contact with the fluid, the receiving end 13' of the receiving element 12 is pushed by the pressurized chamber 15 and the fluid is pushed into the receiving and collecting medium 1 and the fluid genus 1, 0" The fluid receiving element 12 or a chemical in the fluid circuit reacts. The reagent in the body to be injected may be contained in the fluid by the fluid application zone 20 to be injected into the syringe 'or as it is - starting from the application zone 2 due to the wicking effect of the fluid. Introduced, the reagent will move from the source of the dry reagent from injection route j. The drying reagent is preferably in position 4. When the instrument controls the pump, the power to the contact area 8 electrode is turned off or reversed. The pressurized chamber 15 will now push the fluid back into the element 1 and the pressurized gas at the end of the chamber to 15 will expand to fill the cavity, including the gas barrier zone 14 thereby returning to the rest of the syringe. In another embodiment of the syringe and fluid-receiving element, the plenum 15 is expelled to position 16, for example via a hole in the cover element 23 or via a conduit of the sealing element 11. In this example, when the instrument controls the power applied to the electrodes of the injector, the fluid will flow out of the outflow end 3 of the element 1. This fluid replaces the air of the air isolation zone 14 to the discharge end 16 of the plenum 15 and the fluid contacts the fluid receiving zone 13 of the fluid receiving element 12. Since the venting chamber is not pressurized in this example, the fluid is not hit to the component 12. However, the chemicals and reagents in the pump fluid of the syringe, and the chemicals and reagents in the fluid receiving region 13 of the element 12 diffuse. In the contact area 8 electricity 29 1356164 The Republic of China 100 years June 08 bungee instrument control pump power will be reversed until the chamber causes the injection fluid back to the syringe and pull the air back into the gas isolation zone, so that the pump returns Initial rest state. There are other possible configurations of syringes and fluid receiving elements for use in the syringes described above. The second to second s drawings show other methods of connecting the syringe of the present invention with a fluid receiving member. The figure shows a syringe comprising a sealed fluid path, an integrated electrode, a fluid application end, a fluid application region, and an outflow end having a gas isolating member. These compositions are concentrated as shown in the first figure by 100, 1 〇 1 and 102 in the dotted area of the second to second s diagrams. There are four injector configurations and fluid-receiving elements depicted in Figures 2A through 2D. The syringe with the plenum at the outflow end can be connected to the fluid-free receiving element (second and second map) or to one of the three components. It can be connected to a fluid receiving element 118 that is separate and not connected to other fluid circuits (the second B and second F diagrams can be connected to the fluid receiving element 11G' which has a fluid receiving end fluid and the other end is connected to other fluids The fluid path of the circuit 103 (second c and second (}) is connectable to the fluid receiving member 115' which is - both ends of the fluid path are connected to the fluid circuit (105, 1G6 to both ends 115) and The fluid receiving zone is connected. The second A and D-D show fluid-free elements are connected to the closed gas of the injector to 120, while the first E and second figures show that they are connected to the exhaust chamber 130. The figure D is the same as the first figure. An embodiment is constructed in the first figure or the second figure D. The device comprises a transport sample urn strip and a control injection m (four) to the side flow strip. In this example, 115 is a lateral flow. Strips 105 contain the same application area and 1〇6 contain the same outflow area. The side stream strip 115 can contain a capture area, which constitutes a signal-generating microreactor, and the injection stomach is available for 30 1356164 Republic of China 100 Injecting washing liquid, knot, on the 8th of June The body enzyme is subjected to the lateral flow t capture area when performing a ligand binding test. The first to second Q diagrams show how the two fluid receiving elements are connected to the fluid injector. A syringe is depicted in the figure. Parallel connection to the two fluid receiving members in the enclosed plenum. It is also possible to connect a plurality of receiving elements to a syringe in a similar parallel connection when the plenum is vented, but in the second figure. U-图丄 — 与 与 显 显 显 显 显 显 显 显 第 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独 单独The first figure is not connected to a first fluid path element 110, has a -fluid circuit 113 at its other end, and - is connected in parallel to a second fluid receiving element of one of three types. The 2PDQ map shows a fluid receiving region connected to the first fluid path 115, the two ends of which are coupled to the fluid circuits 1〇5, 1〇6, and the second parallel connected to one of the three types. , which may connect three or more fluids in parallel The piece to a single syringe 'in some necessary analytical tests. The second R diagram shows how multiple syringes are connected to a single fluid receiving element. Figure 12, the fluid-receiving fluid path # 115 contains fluid circuits 105, 106 There are three syringes 1 〇〇, ι〇ι and 1 〇 2 injectable fluid in three areas of the full length of the element 115. There is a closed plenum at each of the injection zones 12G, 121 and 122. The three grounding electrodes of the injectors can be independently connected to the separated fluid application region of the fluid application end of the injector element of one of the three, as shown in the second r diagram. More preferably in the second s diagram The grounding electrode of the three syringes will be connected to one of the points of a single fluid application area. It covers the fluid application of all three injectors. 31 1356164 The Republic of China 100 June 〇 8 曰 end. This device can also be completed by a fluid addition conduit. The embodiment shown in the second R and second S diagrams is a device comprising a side flow strip carrying the sample and an instrument controlled multi-injector manifold for injecting fluid into the side flow strip. In this example 115 is a side flow strip, 1 〇 5 contains the same application zone, and 106 contains a sample effluent zone. The sidestream strip 115 can include a capture zone that constitutes a signal generating microreactor. The syringe can be used to inject a fluid containing the reporter combination, the syringe 1〇1 can be used to inject a washing solution, and the syringe 1〇2 can be used to inject an enzyme into the lateral flow strip and pass through the microreaction zone. When a sandwich-type ligand binding assay is required. In general, one of the devices of the present invention comprises at least one instrument-controlled injector connected to a fluid circuit via a fluid-receiving element, reference being made to any of the structures of Figure 1. The device further includes a fluid circuit for introducing the sample fluid into the device, and at least one signal generating a microreaction region. This microreaction zone can be located in the fluid receiving element or the connected fluid circuit. A detector that produces a microreaction near the signal measures the microreaction that occurs during the reaction to determine the concentration of the analyte in the sample. In use, any of the different devices in the second figure will be inserted into the receiving hole of a detecting device, and a flat thick plate embedded in the photodetector is connected to the instrument device. When the device is inserted into the hole of the detecting device, the thick plate is also embedded with a spring that is energized, one end of which is connected to the circuit in the instrument device, and the other end is connected to the electrode contact pad. The receiving hole of the detecting device of the device has a detecting thick plate coplanar and relatively close to the device substrate 10, and the photodetector is located in the microreactor region generated by the signal close to the device. The detection slab forms a partial dark hole with the substrate 10 so that no external light source enters. The apparatus of the embodiment shown in the first figure and the apparatus of the second A to the second S (32 1356164 field 1UU flat UC) month 08 kinds of changes are all built in - standard ^^ φ , ^ ^ The auxiliary electrode on the motor board is powered by 袄, and the body circuit. The device is mounted on the plane! The separated electrodes are gold-plated steel electrodes having (10) 5 milligrams = fiber gold' manufactured by standard circuit board technology. On top of it is a thin layer of 〇25 ς 备 备 元件 元件 元件 , , , , , , , , Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad Ad

Research嶋), which consists of an adsorption difference with an opening in the electrode contact area 5 6 7 (adhesive shee. The opening J of the adsorption thick plate is seen in the electro-optic connection) φ, the first one - the top surface of the metal of the electrode of the contact area is coplanar. The microporous fluid path element U2 is die-cut by a thin layer of about 15 mm thickness per piece. The element ι is about 1 mm wide at the outflow end. As shown in the figure, the element can be a rectangle with a fluid application end of about 1 mm wide. If the fluid application end is wider, a trapezoid is formed. We usually prefer an irregular trapezoid (trapez). 〇 id) pump, the ratio of the width of the inlet end to the outflow end is about 4:1 because it can be pumped at a higher rate. When the π piece 12 carries fluid to the adjacent fluid circuit 21, 22, it can be about ^ The rectangular strip of mm is shown in Figure - although other shapes may be used depending on the particular implementation of the fluid receiving element. When the fluid receiving element is a microreactor, it may be a square or circular thick plate. Fluid element 1 , 12 women have about 0.5 to a few millimeters Above the attachment plate 9 of the gas gap 14, the outflow end 3 of the fluid injection element is separated from the fluid receiving element 12 at a position 13. According to an experimental implementation, the fluid path element 12 can be made of a microporous material. The thin layer is made into a die-cut strip and can be pre-soaked (to block or introduce surface potential) or pre-filled at a special position. The surface treatment of various porous materials and receiving elements is further 33 1356164 For the fluid injection element, a cellulose silicate having a pore size of 〇22 nm is preferred because of its high surface potential required for efficient electroosmotic thrust. Next, the second material is attached. The thick plate 11 is mounted on the microporous fluid path it. The adsorption thick plate u is G15 mm thick and consists of three layers of 0 05 nm thin layer (Adhesive Research 7876) consisting of a thin

The board is die-cut. It covers the element U but does not cover its fluid application end 2, the gas deficiency: zone 14 or its outflow end 3) which covers the part of the element 12 (but not the fluid-receiving zone 13 or the adjacent zone 16). A polymeric film covering member is die cut from a thin layer and mounted over the opening of the second sealing member 11 to define a closed gas pocket 15 by the regions 3, 4, 13, 16 of the first drawing. . The final assembly step 'the flat composition of the slab is smashed for two minutes). The thickener 1 丨 归 会 会 会 ί Ϊ Ϊ Ϊ 之 之 之 之 之 之 之 之 之 之 Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ Ϊ The seal is as shown in the section _ C, as shown in the sectional view. The ί = various configurations are shown in the first and second figures, and the available modes are as follows. The connection to the fluid circuit is directed to the connector. The fluid is aspirated by a syringe to electrolyze: 1. Two syringes of different construction (sinus with the syringe of the second figure) are supplied for exploration. Operating characteristics for special needs: ι. When the fluid is added/injected, it must have the following fibrogenic colony #(10) body's need to be filled from the dry state into a regenerative ft capillary; 2 #无丹过过出端; 3 When electric power is applied to the integrated electrolysis, when the fluid flow rate exceeds the basin flow, the regenerable fluid will be studied for its composition: material surface treatment, fluid path element loyalty from porosity and pore size. 34 1356164 June 08, 100, with the shape and size of the Republic of China. We studied the integrated electrode and its contact area and contact area. We studied the chamber and its pore size, gas gap size, and exhaust structure. When the pump is in operation, the above design parameters are the effect of the initial capillary fluid filling rate. The first step of the flow-stopping effect of the outflow end of the pump component and the characteristics of the electro-osmotic pumping according to the fluid resistance of the component are all discussed. Experiment 1: Injecting the exhaust duct This example was constructed to study the suction characteristics of the injector without fluid injection, the exhaust path at the outflow end, and no other fluid receiving elements. This configuration is shown in Figure 2E, when the syringe is initially pumped by first adding an aqueous fluid to the fluid application end of the initially dry syringe. Next, a voltage is applied between the integrated electrodes, and the flow rate can be known by measuring the length of the fluid in the exhaust conduit at different times and the cross-sectional area of the region. Thereby, electro-osmotic mobility (EMM) can be obtained. Preferably, the fluid of the syringe contains a low conductivity aqueous solution: a concentration of about 2 m Torr (mmol concentration) is preferred, and 10 mM (mole concentration) is the upper end of the range of application. A microporous cellulose nitrate/acetate (Millipore MF membrane GSWP) has a fluid path with a porosity of 0.75 and a pore radius of 0.11 micron as a syringe. There is an integrated positive electrode ground electrode in contact with the fluid application end of the injector and a microporous fluid path that integrates the negative electrode to the injector. A typical injection fluid is a 2 mM aqueous buffer comprising N-(2-hydroxyethyl)piperazine-N-2-ethanesulfonic acid (HEPES) or dihydroxydiethylamine (DEA) buffer. At a fixed voltage of 0-60 volts, the pumping rate is maintained at around 100 seconds. No visible bubbles are formed here in the fluid stream. The effect of pH is maintained between pH &gt; pH &gt; pH &gt; In higher concentrations of electrolyte, the pumping speed is reduced. About 10 mM or more 35 1356164 The Republic of China, June 8, 100 The concentration of the solution will cause the syringe to draw too much current and cannot operate at the voltage rise because the cathode will release bubbles into the fluid. The concentration of the syringe electrolyte affects the pump in two ways. As the concentration increases, the ionic strength also increases and the Debye screening length decreases. This will reduce the interface potential and form a conventional EOM. In addition, a higher electrolyte concentration results in higher electrical conduction of the injected fluid. As a result, when a certain pump voltage is applied, a higher current pull causes a larger electrode polarity. When the electrodes are polarized, most of the voltage will pass through the electrodes and a few will pass through the microporous fluid path components, resulting in a lower pumping rate. The addition of redox molecules to the injection fluid reduces the polarization of the electrode, but limits the generality of the pump as it interferes with the biochemical reaction of the downstream microreactor. When the syringe is operated with the gold electrode and the syringe fluid contains less than 1 mM buffer electrode solution and no oxidizing agent is added, there is no significant electrode polarization. The syringe is filled with syringe fluid: the initially dried microporous fluid path element of a syringe is filled and the field syringe *IL body is added to the fluid application end of the syringe. The fluid acts as a capillary = ~ to fill the S-element to its outflow end. A preferred fluid path material is a microporous cellulose nitrate/acetate having a micron pore size and a 5 mm long syringe loading time of about 5 sec. Position of the integrated electrode: ^ In general, it can be implemented regardless of whether the positive electrode is close to the fluid application end. A preferred embodiment is when the positive electrode is immersed in the outer side of the fluid in the microporous path of the syringe beyond its application end but in electrical contact therewith. The position of the cathode electrode can be anywhere between the fluid path of the micropore of the syringe and the length of the outflow end, but 36 1356164 is preferably located at about half to three quarters of the length from the outflow end. This configuration leaves a zero field area over the negative electrode at the outflow end for the possible location of the dry reagent. When the negative electrode is too close to the positive electrode of the fluid application end, the current will be too high to limit the operation of the device at low voltage and low pumping rate. The typical electrode contact area is 0.5 x 5 mm at the positive pole and 0.5 x 1 mm wide at the negative electrode. Fluid path shape and size: _________长_友整_1|揭____1_1射_器_流_体盖„径_均_灰探封_范_围丄二_典——型形流路元件元件A cellulose nitrate/acetate having a length of about 4.25 mm, a width of 1 mm, and a thickness of 150 μm, having a porosity of 0.7 and a pore diameter of 0.11 μm. A syringe is constituted by the fluid path, the positive electrode of which exceeds the fluid application end, and the negative electrode thereof The fluid application end is about 3 mm (1-25 mm from the outflow end) and operates with 2 mM DEA as the injection. The pumping speed is 0.5 nanoliters per second per volt, which is linear at the applied voltage. At an operating voltage of 40 volts The pumping speed is 20 nanoliters per second. A typical trapezoidal fluid path is about 4.25 mm long, 4 mm wide at the fluid application force σ end, and 1 to 1.5 mm wide at the outflow end. When using the same electrode position with a syringe When the fluid draw rate is operating, it is linear with the voltage at a rate of 1.1 nanoliters per second per volt. The pumping rate is 45 nanoliters per second at an operating voltage of 40 volts. We prefer to use trapezoidal syringes because It has a higher suction speed, but its outflow end with a rectangular syringe Geometrically the same. The size of the outflow end is limited by the size of the fluid receiving element. Fluid path material and surface treatment: Millipore MF membrane GSWP has a 0.11 mm aperture when using a 2 mM DEA syringe Fluid 37 1356164 The Republic of China 100 June 06 曰 'It has a higher and more consistent EOM of about 2_5 X 108 m2 / volt · sec. This is a trapezoidal (rectangular) syringe 1.1 (0.5) nanoliter / sec / volt Consistent. Other research materials have lower or zero EOM. A surface pretreated low EOM material, such as first brewed in an anionic surfactant such as ammonium dodecylsulfonate, and then borrowed Drying can introduce surface charge and enhance EOM. However, it is better to avoid this type of treatment, because the surfactant will be discharged into the injection fluid and enter the fluid to join the children and fluid current, which may biochemical reaction to the position. There are adverse effects here. The luciferase enzymes should be specially/intended later. Since the cellulose nitrate/acetate used above has no surface modification, it is suitable. Used in the syringe fluid path. Experiment 2: Injection into a closed chamber syringe containing a closed plenum at its outflow end, but no other fluid receiving elements were constructed to investigate the suction characteristics of an infinite amount of fluid loaded syringe. First, the syringe is filled with a water-like fluid to the fluid application end that is initially the dry syringe. A voltage is then applied between the integrated electrodes. The fluid will flow from the injector to the initial volume V1 and the flow rate is atmospheric. Replaced by closed pipes. When the fluid fills the chamber, the air is compressed until the steady state fluid stops. The new air volume is V2 less than VI. Finally, the pressure at which the fluid can be stopped can be calculated from Bohr's law P2 = V1/V2. - Microporous fiber dirate/salt with G.11 micron is used. Pore size of the micropore of the syringe: Trapezoidal syringe of microporous cellulose nitrate/acetate (into the end 38 丄 164 BC, June 4, 2010, see 4mm, the outflow end is 1.5mm wide, the length is 4.25mm, the thickness is 0.15 mm) Porosity 0.75 to 0.85 'The pore size is in the range of 〇u to 25 μm. The injector device is located at the outflow end of the enclosed plenum. The voltage of the stop fluid can be measured from 〇 to j 〇〇 volts. The pressure and voltage of the stopped fluid increase almost linearly. Small pore materials require a larger back pressure to stop the fluid than large pore materials. - A syringe with a pore size of 0. U micron is resistant to back pressure at Q17 atmospheric pressure per volt. The typical operating voltage is 4 volts, and the rabbit 1 is stopped. The back pressure of the injection fluid is 〇_〇 1 atmosphere. When the typical operating voltage is 40 volts, the back pressure of the fluid is stopped at 0.4 atmospheres. Sealing the syringe: The quality around the sealed syringe is important to achieve a better flow rate. Disadvantageously sealing the gas passage around the fluid path of the syringe. When the osmotic suction is taken, the result of the difference in the coating force between the outflow end of the syringe and the fluid application end will be less stable and lower than that produced by the channel (4)1. The expected rate of electroosmotic suction. Experiment 3: Injecting a fluid-receiving element into a closed gas chamber in order to investigate the pumping properties of the syringe with a fluid-resistant syringe and a closed gas to the fluid-receiving element; and a fluid-receiving strip element connected to the flow position . Rectangular and trapezoidal notes Two whites are exploring #围. The various steps of the structure of the syringe and the fluid-receiving element, such as the second syringe of this configuration, are shown in Figure 3A. The first fluid is added to the fluid application end of the initial drying strip (Fig.). 4 The drying strip is filled with the first __ fluid due to the side capillary flow (the third injection of the initial first syringe is injected - aqueous fluid (2n 39 1356164 Republic of China 100) From June 8th, DE8th DEA solution) to its fluid application end (third c diagram). The syringe is filled to the outflow end due to capillary flow (third D diagram). A voltage is applied between the integrated electrodes. The outflow end of the syringe is replaced by a closed plenum having a starting volume V1 and P1 = 1 atmosphere. When the fluid fills the plenum, the air enclosing the plenum is compressed until a steady state when compression is stopped (Fig. EE). In steady state, fluid will flow along both ends of the fluid-receiving strip (fluid flow to areas 105 and 106 of the second map), as shown in Figure 3. The volume of air in the newly created chamber is V2 less than VI. The steady state pressure can be calculated by Bohr's law as P2 = V1/V2. After the fluid injection step, the voltage is turned on and the gas in the gas chamber is compressed and returned to the original position at the outflow end of the syringe, and the fluid and fluid are injected. Receiving end Fluid isolation (third G diagram). One of the trapezoidal syringes shown in Figure 4 (inlet width 4 mm, outflow end 1.5 mm wide, length 4.25 mm, thickness 〇.15 mm) uses a microporous cellulose nitrate/acetate As the fluid path of the injection gas (porosity 〇7, aperture 011 μm) and the fluid receiving strip of the microporous polyethersulfone (the fluid receiving area of 1 mm wide, 9 mm long and 1 mm long is at the center position, and extends 4 mm to both ends). , thickness 〇.15mm, aperture 0.25μm). The pressure of the steady flow state increases linearly with the voltage of 〇3〇/pressure. The specification of the syringe: In order to clearly understand how a syringe operates according to the characteristics of the syringe design, Consider a model syringe comprising a syringe fluid path first filled with a capillary machine from the fluid application end to the outflow end. The syringe fluid path comprises a length L, an outflow end width w, a fluid application end width w of a trapezoidal thick plate, and a sorghum Porous material, porosity Ψ, porosity channel curvature τ and aperture a. Here the first electrode is located at the fluid application end of the syringe [or a fluid that exceeds the fluid application end but the fluid Take it). Here there is __Second electrode and syringe fluid 40 - w) Lr\n{W I w)

On the date of June, 2008, the Republic of China, the entrance distance of the path and an area, the length of the outflow end of the zero field area is the L-I zero field area. A fluid viscosity is η, and its flow rate q is as follows. Q = Equation 1 is simplified into Equation 2 for a rectangular sheet of width w.

Q \fhw Lt VMeo Equation 2 When ν is the voltage applied to the length ί and ^. For electroosmotic mobility (the first term is an electroosmotic fluid. When there is a pressure difference ρ along the length of the sheet (positive ρ is - back waste can cause the fluid to call the osmotic fluid in the opposite direction), the second term In order to give pressure to drive the fluid, the velocity of the electroosmotic fluid is separated by the length L instead of the electrode, but at the voltage supplied, the power drawn by the pump increases with the decrease of the I. The pumping rate: The fifth figure shows the The four-characteristic structure and size of the trapezoidal injection-injection-receiving component system--the pump data. The relationship between the fluid catch and the voltage benefit ^ (exhaust operation) shows the triangle data point. Stop the pressure of the fluid and add infinitely (closed outflow The relationship between the gas chambers shows the diamond data points. The relationship between the pressure and the voltage of the injected fluid shows a square data point. The flow of the syringe is 1356164. The fluid conductivity of the body conduction and fluid receiving element GL can be Equation 3 Calculated separately from 4. These equations are obtained from differential trapezoidal injectors and rectangular injection equations 1 and 2. "_dQ _ i^i(W -w)a2 ............ Equation 3 Equation 4 dQ _ {fAiwa1 dP StjLt consists of these equations with known porosity, pore size and component dimensions. As shown in the fourth figure, the conductivity of a syringe is -6.4 nanoliters / second / atmosphere and the total loading conductivity is 27 nanoliters / second / The data lines of the calculated conductivity of the extracted and loaded are shown in the fifth figure. The fluid equivalent circuit and the fluid receiving element of the injector are shown in the fourth figure. The injection velocity is known when connected to the syringe via any receiving fluid element and knowing its flow conductivity. At a predetermined pressure, the intersection of the conductivity line at the time of filling and the conductivity line of the syringe is referred to as the driving fluid in the chamber. The velocity of the gas passing through the receiving element and the velocity at which the liquid flows through the element. The speed of flow through a loading body can be calculated by multiplying the maximum pumping rate at zero loading (during the discharge operation) by GL/(GL+GI). When the conductivity of the syringe is much smaller than the conductivity of the fluid receiving element (including the conductivity of the fluid circuit connected thereto), G1 « GL, the suction rate of the syringe will be connected The maximum pumping rate of the syringe at zero loading (during operation), and the pumping rate is independent of the loading conductivity at which the fluid receiving element and fluid current are connected, and it is particularly important that the injection operation is performed in this example. Between the device and the device, the conduction of the load 42 1356164 The rate of the Republic of China on June 08 will change. The preferred current in the present invention should be designed to operate in a state similar to this. To achieve this syringe conductivity In the state, the GI must be reduced by selecting a smaller diameter material (a in Equation 3), and a larger aperture is required for the receiving element to be connected to the fluid current. The fourth diagram device and its equivalent circuit are further clarified. The maximum pumping rate without loading is subtracted from the loaded rate by a factor of 27/(27 + 6.4) = 0.81. Assuming that the receiving fluid element is initially subjected to a viscosity of 0.001 &lt; η &lt; 0 〇 92 Pa.s _ 间 间 间 巍 = = = = = , , , , , = = = = = 27 27 27 27 27 27 27 27 27 27 / atmosphere, and when η = 0.002 it is 13.5 nanoliters/second/atmosphere. If the receiving element is initially filled with its viscosity η = 0.0002 and receives an injected fluid with η = 0.001, when the fluid with high viscous force is replaced by a fluid with low viscous force, the pumping rate will be 0.68 is increased to its maximum speed of 0.81. The pumping rate will also change with different viscosities of fluids between the machines. The reproducibility of the different loading aspiration rates of a device will be determined by the needs of a particular diagnostic test, but typically a syringe is connected to a receiving element that initially contains the same fluid, and the conductivity of the injector should be less than the conduction of the receiving component. At a rate of 0.05»GI=0.05 GL, the pumping rate is 95% of the maximum pumping rate during venting and remains constant as the loading conductivity changes. The syringe of Figure 4 has a preferred minimum loading conductivity of 128 when GI = 6.4 and a flow rate of 44 nL/sec at a typical operating voltage of 40 volts. The driving fluid in the gas chamber was loaded with a pressure of 0.34 atm. In diagnostic applications of the device, a useful syringe suction rate is determined by the time required to fill a fluid-receiving element, particularly the size of the fluid element, and the time required to fill the fluid-receiving element is determined by the time required for a particular test. A typical fluid receiving element is 10 mm long, 1 mm wide, and 43 1356164. It is 0.15 mm high, with a porosity of 〇7 and a volume of about 1 〇〇〇 nL. A representative pumping speed, i.e., the time required to fill the receiving element, is about 5 sec. or even more than 20 lb/s. Short path pump (L&lt;3mm: This specification can be operated with low voltage (V&lt;12 lbs). Longer path length (3mm &lt;L&lt;6mm) requires a larger voltage (12 &lt; v &lt; 25 volts). The 俨 length (6mm &lt; L &lt; 12mm) requires a larger voltage (26 &lt; V &lt; 5 volts volts). 'Wide gangs, Pu will be transported at a higher flow rate, but if the size of the (4) (four) end is limited by the size of the fluid receiving end The ideal high speed ^·Pu is trapezoidal, that is, the fluid application end is wider and the outflow end is narrower.

Leakage rate:

The syringe of the present invention is characterized in that it has two states: when the power is applied, it is in a stopped state and when the pump power is applied to the integrated electrode, it is turned on. In the initial shutdown state, the syringe is separated from other fluid components by the air gap at the outflow end. In the ideal on state, fluid will flow through the outflow end of the syringe. In the ideal power-on state, the fluid flow rate must be determined only by the applied power of the pump. The fluid connected to the non-injector receives the fluid resistance of the workpiece, and is not between the inlet and the outlet of the syringe when the pump is normally operated. Pressure difference. After the suction is in an ideal state of rest, no further leakage must flow into the syringe, so that the position of the downstream fluid element, such as the microreactor, is stable in the off state. The amount of leakage rate of the syringe in the rest state determines the efficiency of the air gap isolation of the syringe during use of the fluid circuit by the device prior to use of the syringe, and the stability of the fluid position after syringe suction. The air gap is isolated from the size of the crucible so that when the syringe is in a shutdown state (the injector needs to be isolated from nearby fluid receiving elements), the total amount of fluid may leak or leak through the outflow end of the syringe, and the total amount of fluid is not sufficient to Fluid cross-sectional air shortage 44 1356164 The National Insulation Device of June 8, 100 (and contact with nearby fluid components). When a pump that is relatively easy to escape is isolated by a large volume of air gap, it will result in more time to fill a large air gap volume when operating the syringe in the on-state cancer. The rate of leakage of the main emitter is determined by the difference in pressure between the fluid resistance of the syringe and the fluid flow of the syringe in the off-state of the syringe. A pressure differential may occur as the fluid flows through nearby fluid components (typically about 1 〇〇〇〇 pascal or more than 1 〇〇〇〇 scal 气 气 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当 当Element 1 is driven by fluid, such as an adjacent syringe, or when a capillary wick acts as a force with the syringe fluid and the activating surface of the outflow end (smaller, typically 100 Pascal). When a diagnostic device of the present invention comprises a syringe, the syringe is initially filled with fluid (which is now isolated), typically for a period of 200 seconds but sometimes (four) 5 seconds. During this time, when the flow rate of the syringe is the leak rate of the resting state, the isolated area of the outflow end of the syringe is not filled. Further, during the subsequent aspiration process, when the injector is in the open state, the isolation region can be injected into the adjacent fluid-receiving member by the electro-permeable body in a matter of seconds or less. If the column needs to be injected into a blood-sized f-body receiving element in about 50 seconds or less, the typical pumping rate is 2〇nL/Se/, and when the air is about For 10% of the volume of the fluid receiving component (also typical), the I gas deficiency σ takes five seconds to traverse in the power-on state. Therefore, for a useful syringe, the power-on flow rate and the shutdown state of the leakage flow are 200/5=40 ® „, 戎 is larger, but the reduction should also exceed 20. In most cases, such as weeping: from the time interval Long, the state of the power-on state and the state of the power-off state are not leaky. For example, a second isolation time (one syringe flow 45 1356164, the Republic of China 100 years, June 08, the first step of the micro-reactor capture step Time required) In the same geometry where the fluid receiving element is isolated from the air gap, the flow rate to the leak rate must be 1 〇〇. The leakage of the shutdown state after suction can also be determined in the same way. If the fluid volume of the fluid receiving element Filled in the on state for 50 seconds, it must have more than 10% stability compared to the shutdown state of the next 2 sec. The flow rate to leakage rate ratio needs to be 40. If you want to reach 5% For stability, the ratio needs to be 8 〇. In summary, one of the syringes of the present invention needs to have a ratio of fluid to leakage ratio of at least 2 〇, and the general application is about 40,100 is the largest case. Proportion of fluid power to the machine off by Equation 1 can be derived as follows: _ £ _ + 1 = 8 ^

Qy=〇Pa2 .................... Equation 5 β Hai ratio and the hole of the micropore injector fluid path component 3 = operation: differential pressure of the pump voltage V p related. When the syringe is connected to the flow: receiving: the exhaust chamber of the piece, the leakage rate of the syringe is 1 〇 although the syringe is connected to the fluid receiving side 〇Pa ((M atmospheric pressure), the closed 耽 of the body is the body. Shows that we support the pressure-driven fluid velocity ratio in the typical operation of the \Q main aperture and the pressure when not reaching the first-class lake is as follows: for the voltage and the ratio is 46 1356164 Republic of China 100 years June 08 曰 &lt; Pa .s 0.001 &lt;eo m2 / V .s 2E-08 P = 100 V volts 1 5 9 12 40 100 20,000 50,000 Q/Qv=〇= 40 &lt;3 &lt;m 0.20 0.45 0.60 0.69 1.3 2.0 28 45 Q/ Qv=〇=100 0.13 0.28 0.38 0.44 0.8 1.3 18* 28 P = 10000 V volts 1 5 9 12 40 100 20,000 50,000 Q/Q v=〇= 40 &lt;a &lt;m 0.02 0.04 0.06 0.07 0.13 0.20 2.8 4.5 Q /Q v=〇=100 0.01 0.03 0.04 0.04 0.08 0.13 1.8 2.8 This table shows a syringe with a discharge effluent using EOM= 2 X 1 (T8 m2/volt-second material with a viscosity of 0.001 Pascal- Second water injection operation, when the special operation is between a start-up and a suspension fluid ratio of 40 (100) and must fight one The lOOPascal differential pressure must have a lower voltage operation with a pore size less than 2.0 (1.3) microns and less than 100 volts, preferably less than 0.7 (0.4) microns for a 12 volt battery operation and 0.4 (0.3) microns for a 5 volt operation. Preferably, a syringe having a closed chamber at the outflow end undergoes a pressure difference of 1 〇, 〇〇〇 Pascals and operates at 40 volts in general requires a material having a pore size of 0.13 μm or less. The small aperture will not be used in standard lateral flow diagnostics and will not be used in lab-on-a-ch ip technology for the open-path construction of microporous materials in electroporation pumps. The path consists of a syringe, typically used in a microfluidic device built on Lab-on-a-chip technology, operating at 20,000 volts to achieve a typical required fluid velocity ratio of 40, at 50,000 volts. Up to 100. Therefore, the standard open-path pump of the conventional laboratory wafer is not able to pass the air described in the current invention due to the leakage fluid that easily affects the state of the suspension. The passive gap of the Republic of China on June 08, 100 Valving means to control, and therefore need to use actively closed - means. Laboratory data generally supports the module calculations indicated above. Very little leakage from small aperture injection materials. The isolation effect of the syringe in the off state is less preferred if the pore size is larger than a few microns, especially if the gas chamber surface is activated near the outflow end of the syringe or has a surfactant in the injection fluid. Loading Fluid from the Integrated Storage Tank to the Syringe • The fluid component of the present invention comprises a syringe with integrated electrodes and a fluid circuit coupled thereto, which can be integrated into a plastic card reader and also includes an integrated sealed fluid reservoir containing a fluid filled with a syringe groove. A card reader having a fluid assembly and an integrated fluid reservoir includes a single step device having all of the fluid required for testing in a single integrated unit. The fluid component of the present invention can be constructed on a standard printed circuit board substrate as shown in the first to fourth figures. In this example, the electrical contact position of the electrical is integrated to the same side of the external contact tool and fluid as the component substrate. The fluid assembly can also be constructed on a bilaterally contracted circuit substrate having through-substrate electrical connection vias through the substrate so that the fluid circuit can be constructed on the surface of the shrink substrate And the contact area to the external contact tool is located on the lower surface. A preferred structure is obtained when a credit card sized card housing is added to the fluid element, as shown in Figures 6 and 6A. The device of the sixth diagram is a top view of a credit card sized diagnostic card having a fluid element and a sealed fluid storage slot embedded therein. Figure 6A shows a side view of the AA' and BB' cut planes of the sixth figure. The fluid element has the same fluid configuration as shown in the second S-picture, except that the syringe is trapezoidal and the integrated electrode is connected to the outside of the substrate by the substrate from the substrate on June 08, 100. The diagnostic card contains a plastic card housing 601. The outer casing has a fluid storage recess 604 with a polyethylene foil coated with aluminum foil above and below. The groove contains a low conductivity aqueous buffer. The reservoir fluid is sealed by a polyethylene wire fused with aluminum wire. The card housing also includes a drinking fountain 603 having an entry end to the valve tool 606 and an outflow end 605 having an air vent 613. The card housing further includes a void 602 for receiving the fluid module 600. _ Stream search ghost 6_00_包_含_一_epoxy gold_genus_#_021____ The base of the substrate is both metallized by gold plating. At the fluid end above the substrate of the module, the metal has formed integrated electroosmotic suction electrodes 623 and 624, 624A, 624B for contact with the injector. The lower metal forms pads 621 and 622, 622A, 622B for contact with external electronic contact tools. There are four metallized holes (two of which are 625, 626 shown in Figure 6A), connecting the upper electrode electronics to the underlying liner via an epoxy matrix. The epoxy module and electrode are fabricated by conventional standard shrink loop circuit technology. Here, a first sealing tool 627 is a film-cut attachment member located on the upper surface of the epoxy module. Element 627 covers the surface of the module but does not include 623, 624, 624A and 624B where the integrated electrode is in contact with the fluid element of the injector. There is a microporous strip element 629 over the first sealing layer. Element 629 has the same application end 640 and a fluid collection element 641 of known fluid fill volume at the outflow end. There are also three micropore syringe path elements 628, 628A and 628B having an outflow end separated from the strip element 629 by a gas gap at three fluid receiving locations throughout the length of element 629. The injection route member has a trapezoidal shape with a wide fluid application end and a narrow fluid outflow end. A second sealing member 630 covers the microporous fluid element but does not contain the fluid application end and the outflow end, and also excludes the fluid receiving region 629 of the gas chamber including the gas gap and the outflow end of the syringe. A surrounding seal is formed. 49 1356164 Around the microporous element, the sealing elements 627 and 630 were compressed around them. In the final assembly, the fluid module 600 is inserted into the housing aperture 620 and sealed. The card is further sealed to the upper film cut sheet 610 and an lower film cut sheet 611. In the first step, the outer casing member encloses the air chamber of the outflow end of the syringe on the fluid module and encloses the cast drinking trough 603 in the plastic card to form a fluid path. When the same fluid is applied to the sample application end 640 of the element 629 and it passes the strip through the capture zone 660 and into the fluid collection element 641. One of the sample fluids is to be captured in the capture area. Next, the card is inserted into the card hole of the device tool. The card aperture has a planar surface and includes a slab having an element that engages a lower end of a card. When the card is inserted, the lower surface of the card is parallel to the surface of the thick plate of the card insertion hole and is separated. The slab has an electronic contact pad embedded in the spring-contacting electronic module adjacent the module and two raised regions adjacent the fluid reservoir 604 and valve 606 of the card when the card is inserted into the hole of the card. In the hole, the card is brought down to be in contact with the slab. The contact electronics with the magazine are now in contact with the electronic contact pads of the module. The first slab rises in contact with the card at position 650 and pushes the plug 606 through the hole 607 of the card cover, thereby separating the top sheet seal of the position 608. The second slab rises into contact with the card at position 651, depressing the fluid reservoir and replacing the fluid entry path 603 via the separation seal region 608. The fluid displaced into the path fills the outflow end 605 of the region 603A. Region 603A is the application area for the injection fluid. The fluid in this region now fills the syringe from the fluid application end to the outflow end via the capillary wick phenomenon. The dried reagent at the outflow end of the syringe is dissolved by capillary filling. An instrument control voltage is applied to the first injector electrode 624A to contact the fluid application region 603A with respect to a common auxiliary electrode 621, such that a first fluid containing a 50 1356164 enzyme-labeled conjugate dissolved on June 08, 100, is electrically infiltrated. Injection along a strip 629 comprising a capture zone 660 to an outflow path 670. A calibration complex is captured by the analyte at position 660, thereby calibrating the capture complex. A second instrument control voltage is applied to the second injection electrode 624 such that a second effluent is injected along the strip containing the capture zone by electroosmosis. The cleaning fluid removes the conjugate that is not redundantly bonded. A third instrument control voltage is applied to the third injector electrode 624B such that a third fluid containing the enzyme matrix is infiltrated by the cap. When the substrate is chemically generated ____________; the phosphor, the substrate and the position 660 enzyme calibration produces a light signal that can be measured by a light detector that is near the card position 660 and detects the &lt;§ light signal It is proportional to the concentration of the analyte in the sample. Experiment 4: Electroosmotic injection of luciferase chemical fluorescent reagent The construction of the syringe in this experiment is similar to that shown in the second Q diagram except that the exhaust chamber is used. In the device, the syringe is a trapezoidal element having a hole of 1 mm at the outflow end, a hole of 4 mm, a length of 4.25 mm, a thickness of 0.15 mm, a microporous cellulose nitrate/acetate, a porosity of 0.7, and a pore diameter of 0.11. There is a venting chamber having a 1 mm wide passageway at the injector outlet end, the syringe containing a 〇.5 mm long gas gap separating the outflow end from the first fluid receiving element. The first fluid receiving element is a side flow strip, and has a fluid receiving area, the same application end, and an outflow end in the center. This element is a 0.15 mm thick, 1 mm wide, 8 mm long micropore cluster with a porosity of 0.7 and a pore size of 0.25 microns. Here a second fluid receiving element is separated from the first fluid receiving element by a further 0.5 mm air gap. The second fluid-receiving member is a reaction zone comprising a polyether liner, 15 mm thick, 2 mm long and 2 mm wide, filled with a fluid containing ATP, luciferase, magnesium ions and buffer and which may be dry. Test reagents were purchased from Sigma. 51 1356164 The Republic of China was placed on the insertion hole of the equipment tool. The A sample fluid containing the fluorescein test was added to the fluid receiving end of the first fluid receiving element, and filled with 2 mM water-containing DEA. The syringe fluid is directed to the fluid application area of the syringe. The fluid fills the two components to their outflow end. When each element is filled with fluid, an instrument control voltage (40 volts) is applied to the integrated electrode of a syringe and fluid is drawn out of the outflow end of the syringe (at 45 nanoliters/second). The injection of the fluid stream for a period of time (about 20 seconds) in the first injection step is sufficient to flow through and cover the fluid receiving area of the first body receiving member. However, it does not reach the second fluid receiving element, at which point the syringe voltage has been turned off. At this time, the fluorescein of the fluid receiving region of the fluid receiving member diffuses into contact with the injected fluid. Applying a voltage (40 volts) to the syringe for a second injection step in the second injection step allows the fluid to move farther away, so that it can be located beyond the second fluid receiving element. Here, a luciferase in the injection fluid reacts with the luciferase of the second fluid-receiving element to generate a light signal, which is detected by a photodetector close to the second fluid-receiving element (5mm X 5mm area light II) A polar body with a photocurrent output of 109 volts per ampere; provided by EOS). A set of identical diagnostic devices was used to test various concentrations of luciferin samples in serial dilutions of buffer. The Moiré number of luciferin in this test reaction is obtained by multiplying the concentration of the fluid volume of the syringe fluid strip. The dose response curve of the luciferin Moir number is linear with the light signal in the range of 6 x 10_14 to 6 X 1 CT11 moles, and the detector output with 4mV detector sensitivity is picomole luciferin. This demonstration experiment was used to determine the second step detection sensitivity in the two-step procedure. The two-step test procedure will be calibrated using a one-base phosphatase assay in a sandwich assay, and the labeled analyte complex will be formed in the sample fluid strip capture zone, first step 52 1356164 Fluorescence in the steps of the Republic of China on June 08 The phosphoric acid matrix is injected into the capture zone by electroosmosis to produce luciferin. In the second step, the luciferin is transported to a second fluid-receiving element where it reacts with luciferase to produce a detectable light signal. Based on the variability of the baseline 2SD of the detector at 8 microwatts, the luminosity limit above 2 X 1 〇 _15 can be detected. The wall enzymease label produced by luciferin citrate produced 1000 moles/sec of luciferin when we cultured for 1 sec. after labeling. The expected limit is 2x1〇-2Q Mohr. 10 microliters of sample fluid contains a concentration

~ One Hx_ on 0^5^—j produces two sensitized analyte molecules containing 2 X 10 Mohr-labeled molecules labeled with a base phosphatase molecule. When the analyte is completely captured in the capture position, the position will have 2 X 1 〇 20 moles of the captured base phosphatase. The detection limit of the detector is determined by the sensitivity of the detector. The sensitivity is about 2xi〇-15|\/j in a 10 μl sample volume. Experiment 5. Electroosmotic injection of diox xetane matrix to generate base phosphatase chemical fluorescence This experiment, using a syringe structure similar to that shown in the second j diagram above, except for an exhaust chamber. In the present apparatus, the syringe is a trapezoidal member, and the outflow hole is 1 mm wide. The input hole is 4 πιηη, the length is 4.25 mm, and the thickness is 0.15 mm. The microporous cellulose nitrate/acetate is contained, the porosity is 0.7, and the pore diameter is 0.11. There is a venting chamber having a 1 mm wide passageway at the outflow end of the syringe, containing a -05 mm long gas gap separating the outflow end from the first fluid receiving element. The first receiving element is a dry reagent addition zone containing a phosphatase for the fluorescent dioxetane (CDP-star is commercially available from Tropix Inc). Here, a second fluid receiving member is separated from the first fluid receiving member by another 0.5 mm gas gap. The second fluid receiving member has a fluid receiving region in the center of one side of the flow bar, a sample application end and a first-class output end. The second fluid receiving element is a reaction zone. 53 1356164 The country is a 0.15 mm thick, 1 mm wide and 8 mm long microporous nylon having a porosity of 0.7 and a pore diameter of 0.25 mm. The component was treated with a BSA barrier of standard operating procedures prior to assembly. The device is inserted into the insertion hole of the device tool, a sample fluid containing the base phosphatase test is added to the fluid receiving end of the first fluid receiving element, and a filling injection fluid containing 2 mM water DEA to the syringe fluid Apply area. The fluid fills the two components to their outflow end. When each element is filled with fluid, an instrument control voltage (40 volts) is applied to the integrated electrode of a syringe and fluid is drawn out of the outflow end of the syringe (at 45 nanoliters/second). After the fluid flow is injected for a period of time (15 seconds) in the first injection step, it is sufficient to flow through the fluid receiving area of the first body receiving member and cover it, but not to the second fluid receiving member, at which time the syringe voltage has been turned off. At this time, the fluorescein of the fluid-receiving region of the fluid-receiving member diffuses into contact with the fluid to be injected. Applying a voltage (40 volts for 20 seconds) to the syringe during the second injection step allows the fluid to move farther away, so that it can be located beyond the second fluid-receiving element. Here, a dioxycycloalkyl group in the injection fluid reacts with the base phosphatase of the second fluid-receiving element to generate a light signal, and the signal is received by a photodetector close to the second fluid-receiving element (5 mm X 5 mm area) The photodiode has a photocurrent output of 109 volts per ampere amplification; provided by EOS, Inc.). A set of identical diagnostic devices was used to test various concentrations of base phosphatase samples diluted by a series of buffers. The number of moles of base phosphatase in this assay reaction is obtained by multiplying the concentration by the volume of fluid in the syringe fluid strip. The dose response curve of the Moir number of the base phosphatase and the light signal are linear in the range of 1 x 1 (T14 to 1 X 1 CT18 moles, with the detection of ΙΟΟμν 54 1356164 The sensitivity of the detector output of the Republic of China on June 08 The enzyme acylase of Atmox 1 e. This demonstration experiment was used to determine the sensitivity of the base phosphatase label for sandwich-type ligand binding assays. Based on this detector 5 microwatts Baseline 2SD variability, limited to 5 X 1 (Γ15Μ can be detected in base phosphatase or lOpL sample solution above 5 X 10_2Q Mohr. Experiment 6: Capturing bound biotin (Biotin) to assay ligase The region label is captured by Streptavidin, and the dioxetane is extracted by electroosmosis to generate a signal _________________________________ This is a ligand binding assay paradigm completed in a lateral flow strip providing a fluorescent matrix injector. In this experiment, a syringe structure is similar to that shown in the second I diagram above. In this device, the syringe is a trapezoidal element, the outflow hole is 1 mm wide, the input hole is 4 mm, and the length is 4.25 mm and the thickness is 0.15 mm. Containing microporous cellulose nitrate/acetate with a porosity of 0.7 and a pore size of 0.11. There is a venting chamber with a 1 mm wide channel at the outflow end of the syringe, including a 0.5 mm long gas gap to the outflow end and the first The fluid receiving element is separated. The first receiving element is a dry reagent addition zone containing a fluorescent dioxin ring-burning matrix (CDP-star from Tropix Inc.) used by the test enzyme lysing enzyme. The fluid receiving element is separated from the first fluid receiving element by another 0.5 mm gas gap. The second fluid receiving element has a fluid receiving area in the center of the side flow strip, the same application end and the first-class outlet. The second fluid receiving element A 15 mm thick, 1 mm wide, 8 mm long microporous nylon with a porosity of 0.7 and a pore size of 0.25 mm. This element was initially filled with streptavidin to a 1 mm long capture zone in the center of the strip. (by immersing in 600 nanoliters of fluid, the fluid contains 10 mg/liter of solution), and then before installing the device, SUPERBLOCK (Pierce Biotechnology Inc) according to its operating manual 55 1356164 Republic of China 100 years 06 The procedure recommended on the 08th is blocked. The device is inserted into the insertion hole of the device tool. 6&quot; L contains a certain concentration (usually 0.1 to ·50ρΜ) combined with biotin and alkaline phosphatase label is added to the second fluid receiving The fluid receiving end of the element, with a fill injection fluid containing 2 mM water DEA was added to the fluid application area of the syringe. The fluid fills the two components to their outflow end. When each element is filled with fluid, an instrument control voltage (40 volts) is applied to the integrated electrode of a syringe and the fluid is drawn out of the outflow end of the syringe at a rate of 45 nanoliters/second. At this injection step, the fluid stream is injected for a period of time (15 seconds) sufficient to flow through the first body receiving member and cover it, at which point the syringe voltage has been turned off. At this time, the fluorescent dioxycycloalkyl group of the fluid receiving region of the first fluid receiving member is diffused to be contacted with the injected fluid. In the second injection step, a voltage (40 volts for 20 seconds) is applied to the syringe to move the fluid farther away, so that it can be located above the second fluid receiving element. Here, there is a dioxoalkyl group in the injection fluid and a base phosphatase reaction of the second fluid-receiving element to generate a light signal, and a photodetector close to the second fluid-receiving element (a light dipole of 5 mm X 5 mm area) The body has a photocurrent output of 109 volts per ampere amplification; provided by EOS. A set of identical diagnostic devices was used to detect a range of buffer-diluted samples of various concentrations of biotin combined with base phosphatase. In this test, the vacuum tube signal sensitivity of ΙΟΟμν is a linear reaction between picomolae and biotin concentration. The detector's 5 microwatt baseline 2SD variability determines the detection limit to 5 X 1 (Γ14 Μ can be detected. Experiment 7: Capture binding biotin (Biotin) to base phosphatase in Streptomyces Streptavidin captures the regional marker and uses electroosmotic to absorb the dioxetane to generate the signal 56 1356164. This is a ligand binding assay paradigm on the side of a fluorescent matrix syringe. The second structure completed by the flow bar. In this experiment, a syringe structure is similar to that shown in the second figure I. In the device, the syringe is a trapezoidal element, the outflow hole is 1 mm wide, the input hole is 4 mm, and the length is 4.25. Mm is 0.15 mm thick and contains microporous cellulose nitrate/acetate with a porosity of 0.7 and a pore size of 0.11. There is a closed gas chamber at the outflow end of the syringe where it is connected to the two fluid receiving elements. The chamber is 0.6mm wide, and the 200 &quot;m high passage is connected to the outflow end of the syringe to cross the two bodies for the _&amp; and the tail end is a closed air chamber of 2 mm wide, 10 mm long and 200 high; There is a 0.5mm gas shortage here. The mouth separates the outflow end of the syringe from the first fluid receiving element of 0.6 mm width and 1.5 mm length. The first fluid receiving element is a dry reagent addition zone containing a fluorinated epoxy cycloalkyl group for acid absorption with the test group. Enzyme reaction (CDP-star from Tropix Inc.) where a second fluid-receiving element is separated by another 0.15 mm gas gap. The second fluid-receiving element has a fluid-receiving area in the center of one side of the strip, the same application end. With a first-class origin, the component is a 0.15mm thick, 1mm wide, 8mm long microporous nylon with a porosity of 0.7 and a pore size of 0.25mm (Osmonics: Magna MEMBRANE). 〇This component was originally added with streptavidin. A capture area of up to 2 mm wide and 1 mm long is between the central fluid receiving zone and the effluent zone of the strip (by infiltrating 600 nanoliters of fluid containing 10 mg/liter of solution), before installing the device The barrier is treated with SUPERBLOCK (Pierce Biotechnology Inc) according to the procedure recommended in its operating manual. The device is inserted into the insertion hole of the device tool. 6m L contains biotin combined with alkaline phosphatase label A certain concentration (usually 0.1 to 50 pM) is added to the fluid receiving end of the second fluid receiving element, and an injection fluid, 57 1356164, the fluid of the Republic of China on June 8, 100 contains 2 mM water DEA, which is applied by the fluid added to the syringe. The fluid is filled to the two components to its outflow end. When each component is filled with fluid, an instrument control voltage (40 volts) is applied to the integrated electrode of a syringe and the fluid is drawn out of the outflow end of the syringe at a rate of 45 nanoliters/second. . At this injection step, the injection fluid stream is sufficient to flow through the first body receiving member and cover it for a period of time (15 seconds), at which point the syringe voltage has been turned off. At this time, the fluorescent dioxycycloalkyl group of the first fluid receiving member diffuses to contact the injected fluid. In the second injection step, a voltage (40 volts for 20 seconds) is applied to the syringe to move the fluid farther away, so that it can be located beyond the second fluid receiving element. Here, a dioxycycloalkyl group in the injection fluid reacts with the base phosphatase in the capture complex of the second fluid-receiving element to generate a light signal, and is detected by a photodetector (5 mm x 5 mm area) close to the second fluid-receiving element. The light diode has a photocurrent output of 1010 volts per ampere; provided by EOS). A set of identical diagnostic devices was used to test samples of various concentrations of biotin mixed with base phosphatase diluted in buffer. The sensitivity of the vacuum tube signal of 243famp in this test is a linear reaction between the micro moir and the biotin concentration. The detection limit of the detector's 5 microwatt baseline 2SD variability is limited to 4x 10_15 Μ can be detected. The embodiments of the present invention described above are merely examples. Variations, modifications, and variations may affect the particular embodiments, but are not intended to be included in the scope of the invention. 58 1356164 The following is a schematic view of a preferred embodiment of the present invention showing an instrument-controlled electroosmotic injector comprising an integrated electrode connected to a fluid-receiving element in accordance with a preferred embodiment of the present invention. The first A-Η diagram shows that the instrument controls the electroosmotic syringe to include an integrated type—the electric 尨 is a 其 其 其 其 其 其 其 其 其 其 单 单 单 单 单 单 单 单 单 单 单 单 单 单 单 单 单 。 。 。 。 。 。. The second I-Q diagram shows a top view of the instrument control electroosmotic syringe including an integrated electrode and two different parallel connected fluid receptor component modes. The second R-S diagram shows that the plurality of instruments control the electroosmotic injector comprises a combination of two electrodes and two different fluid receiver elements in a parallel manner. ' Body Attachment The second A-G diagram shows a top view of the syringe's fluid injection operation connected to the flow. The fourth A-B diagram shows an equivalent circuit top view of the syringe connected to the fluid receiving element containing the millimeter size and fluid flow of the device, respectively.

The fifth figure shows the fluid characteristics of the device of Figure 4A. The sixth figure shows a one-step diagnostic card combination with a plurality of multi-injection sample fluid paths and a sealed storage top view incorporating the original fluid of the syringe. Figure 6A is a cross-sectional view showing the diagnostic card of the sixth figure. [Main component symbol comparison description] 1 Microporous fluid path component 2 Fluid application end 59 1356164 Republic of China 100 June 08 3 Outflow end 5 Pad 6 Contact area 7 Pad 8 Contact area 9 First sealing element 10 Substrate 11 Sealing element 12 first sealing element 13 fluid receiving area 14 air insulating element 15 gas chamber 20 fluid application area 21 fluid circuit 22 fluid circuit 23 fluid circuit 22 covering element, fluid circuit 23 covering element 103 fluid circuit 105 fluid circuit (fluid receiving element 106 fluid circuit (fluid receiving element) 110 fluid receiving element (fluid path element) 113 fluid circuit 115 fluid receiving element (side flow strip, first fluid path) 118 fluid receiving element 120 closed air chamber, injection area 1356164 Republic of China 100 years June 08 121 Injection area 122 Injection area, 130 Exhaust chamber. 600. Fluid module 601 Plastic card housing 602 Cavity 603 Drinking trough 603A Flowing car monument area bee _ (Fluid application area) ___ _______________ 604 Fluid storage groove 605 valve tool (outflow end) · 606 valve 607 card cover hole 608 Separation position 610 Upper chopping sheet 611 Lower film cutting sheet 613 Pore 620 Epoxy sheet 621 Pad (common auxiliary electrode) 622 pad® 622A pad 622B pad 623 Integrated electro-osmotic suction electrode 624 Integrated electro-osmosis pumping Suction electrode 624A integrated electro-osmotic suction electrode 624B integrated electro-osmotic suction electrode 625 metal-plated hole 61 1356164 Republic of China 100 June 08 626 Shovel metal hole 627 Sealing element 628 Micro-pore syringe path element 628A Micro-hole syringe path element 628B Microporous Syringe Path Element 629 Strip Element 630 Second Sealing Element 640 Sample Application End 641 Fluid Collecting Element 660 Capture Area 670 Outflow Path

62

Claims (1)

1356164 The following patent scope: L. A syringe pump for transporting fluid to a fluid receiving location of a fluid receiving component, comprising: an initially dry fluid path having a fluid application end For receiving fluid, and a first-class outlet for transporting fluid to the receiving position, by applying a fluid to the application end, the fluid path is filled with fluid to the outflow end by capillary flow; ----------- The second 璺_%_ is configured to electrically convert the fluid out of the outflow end of the fluid element to the fluid application position; and a sealing element to seal along the periphery of the fluid path to prevent the fluid from being vented by the fluid path Flowing around. = The syringe pump of claim i, further comprising an insulator for isolating the outflow end from the receiving position to prevent passive fluid from flowing out of the outflow end as the fluid passes through the containing fluid. &lt; 3. The syringe pump of claim 2, wherein the insulator is a gas gap adjacent to the outflow end. 4. The syringe pump of claim 1, wherein the initially dry fluid path is made of a microporous material and is wetted by capillary action when the fluid is added to the end. From an integrated flow channel, more preferably an integrated fluid storage tank that is initially sealed, and then the rupture rupture releases fluid to the application end of the fluid path. The syringe pump of claim f, wherein said stream is made of a material having a surface charge and an interface potential. The syringe pump of claim 1, wherein the drive f is a pair of separate first and second electrodes 'to provide an electronic electricity-fluid path fluid' preferably one of less than 100 volts Potential 63 1356164 The operation of the Republic of China on June 8, 100. 7. The syringe pump of claim 6, wherein the first electrode is in electrical contact with the fluid in the fluid path in a first position, preferably at the time of sub-permeation suction. The ends are spaced apart so that the (7) L of the fluid path produces a zero field region, and the second electrode is located at - the second and the separation region is in electrical contact with the fluid at the application end. 8. The syringe pump of claim 6 or 7, further comprising a contact element for electrically connecting the first and second electrodes to an electronic control instrument to generate an electronic potential, preferably one The electronic circuit board has contact points for electrically connecting the control instrument, and an electronic conductor is used to electrically connect the first and second electrodes of the contact element. 9. The syringe pump of claim 6 or 7, wherein the first and second electrodes are partially bendable electrode modules. 10. The syringe pump of claim 3, wherein the fluid receiving element is selected from the group consisting of a microporous lateral flow path, a conduit, a microreactor, and a chamber. 11. The syringe pump of claim 2, wherein the fluid receiving member comprises a first fluid receiving member, comprising a dry reagent circulating when a receiving device receives fluid from the syringe pump, and a second fluid receiving member, the fluid contacting the first fluid receiving member for receiving an injection fluid comprising the flow-through reagent. The syringe pump of claim 1, wherein the fluid path lightly contains a flow-through reagent, and when the fluid is added to the application end, the reagent flows through the capillary fluid along the length of the microporous fluid path. And delivery, preferably a reagent selected from the group consisting of fluorescent, luminescent, electroluminescent, and chemically fluorescent matrices and combinations thereof. 64 1356164 The invention relates to a syringe pump according to claim 3, wherein the microporous fluid path has a hole having a radius of less than 1 micron, preferably less than 02 micrometers. The syringe pump of claim </RTI> wherein the osmotic pumping fluid has an electrolyte having a concentration of less than 10 millimoles. 15. The syringe pump of claim 1, wherein the fluid passage is lightly trapezoidal and has a fluid application end that is wider than the outflow end.丄6一. 免申露露1 第第jh—毛射m—very—中一前益益_________ The fluid flow of the fluid-filled body is at least 20 times smaller than the fluid conduction at the fluid receiving position of the fluid-receiving element. Φ 17. The syringe pump of claim 1, which is for providing fluid to a helium chamber at a fluid receiving position or a closed chamber at a fluid receiving position. 18. The syringe pump of claim 1, wherein the fluid receiving element is a microporous side flow strip having a fluid receiving position along the length, preferably the side flow strip has A sample application end and a first-class end. 19. The syringe pump of claim 1, wherein the fluid body is introduced into the application end of the initial dry fluid path and supplied to the application end by an integrated fluid storage tank. a micro-test apparatus comprising: a microreactor; a first fluid element for introducing a sample into the microreactor; and a syringe pump as claimed in any one of the preceding claims 1 to 19 The micro-test device according to claim 20, wherein the first fluid element is used to introduce the sample into the micro-reactor system, a microchannel, and a microporous device. It is initially dry and contains a circulating reagent. 22. The microtest device of claim 2, wherein the microreactor is located along a length of the first fluid element. The micro-test apparatus of claim 20, wherein the first fluid element and the fluid path element of the ejector pump are formed on a planar substrate. The micro-test apparatus of claim 20, wherein the first fluid element and the fluid path element of the aforementioned left-hander pump are formed in a film-cut manner from the film layer. 25. A micro-test apparatus comprising: an electronically insulating substrate; at least one microreactor; an N-input fluid path network for providing fluid to the microreactor; and a flow-out fluid path network for removing micro The fluid of the reactor; and the network of at least one of the helium input fluid paths, the helium effluent fluid path network is a syringe pump as described in any one of the aforementioned claims 1 to 19. 26. The microtest device of claim 2, wherein the outflow end of the fluid path of the syringe pump, the gas gap, and the first fluid element for introducing the sample into the microreactor It is sealed in a closed chamber containing gas and separated from the periphery, or sealed in a closed chamber containing gas and discharged through a gas valve path. 27. The microtest device of claim 25, wherein the fluid receiving component is a microporous side flow strip having a fluid receiving location along its length. 66 1356164. The micro-test device of claim 25, wherein one or more of the aforementioned N-input fluid path networks, the μ-outflow path network is initially dried and contains A flow-through reagent, preferably a reagent, is selected from the group consisting of fluorescence-producing, luminescence-producing, electro-chemical fluorescent matrices, and combinations thereof. 29. The microtest device of claim 25, wherein the one or more microreactors are a channel for fluidly connecting to an area of the first fluid tool or to the syringe pump One of the fluid paths. 30. The microtest device of claim 25, wherein the one or more microreactors are located along the length of the helium entering the fluid path or along the length of the helium outflow fluid path. The microtest device of claim 25, wherein the one or more of the helium effluent fluid paths or the ν inlet fluid path is a microporous element that is initially dried and contains a flowable reagent. 32. The microtest device of claim 25, wherein the one or more of the first input fluid paths or the helium flow path is a capillary size&apos; and is produced by microprocessing of the planar substrate. 33. A diagnostic device with integrated fluid, comprising: at least one lateral flow element having a first end for sample fluid application and an &quot;one outflow end; at least one microreactor for chemical reaction along a length of the lateral flow element And a syringe pump as described in any one of the preceding claims, to selectively provide a fluid to the microreactor. 34. The diagnostic device of claim 33, wherein the at least one lateral flow element is an initially dried porous element comprising a flowable chemical. 67. The method of claim 34, wherein the circulatory reagent is a labeled combination. The diagnostic device of claim 33, wherein the outflow end of the fluid path member of the syringe pump, the air gap and the fluid receiving position of the side flow member are sealed to a closed chamber containing gas. 37. A diagnostic device having an integrated fluid detectable analyte in the same fluid, comprising: an electronically insulating substrate; a microreactor on the substrate; at least one lateral flow element for providing a microreactor The conjugate is reported to form a complex of the analyte and the conjugate; a fluid element is used to provide the sample to the microreactor; and a syringe pump is described in the patent application scope of any of the preceding items 1 to 17 a fluid receiving location for providing reagents to the microreactor. 38. The diagnostic device of claim 37, further comprising a tool for detecting complex formation of the analyte and the conjugate. 39. An integrated diagnostic device for testing a concentration of an analyte in a sample fluid, comprising: a microreactor for capturing a complex of an analyte and a conjugate; a substrate having a basic lateral flow component for Carrying the analyte in the sample solution to the microreactor; and at least one supplemental fluid path for providing a reagent to the microreactor, the supplemental fluid path being a syringe pump as in any one of the foregoing items 1 to 17 The scope of the patent application is described. 40. A diagnostic device comprising: a card body; 68 1356164 The first microporous fluid path of the first dry period of the Republic of China is set on the card body with a fluid application end and a first-class outlet; a sealed fluid storage and storage a slot is disposed on the card body; a valve for selectively opening the sealed fluid storage tank for releasing the storage fluid from the storage tank; and a guide fluid chamber for providing fluid release to the micropore fluid path end. Two dream devices, including a _________ side flow strip comprising the same application end and a first-class outlet, and at least one/gut body receiving position along its length for receiving fluid by an instrument control fluid injector; and a closed gas The chamber is in the fluid receiving position. 42. A microfluidic device having at least one electroosmotic pump, comprising: a fluid path having an interface potential on a surface thereof electrically connected to a pair of separate electrodes at two separate electrode locations, wherein the separate electrode spaces are formed in insulation The end of the substrate, and j_, is electrically connected via a substrate to two separate contact regions formed at the other end of the insulating substrate for connection to an external instrument for generating an electron potential through the electrode. 43. The microfluidic device of claim 42 wherein said insulating substrate is a flexible metal foil. 69 1356164 The Republic of China 100 years June 08 曰 VII. Designated representative map: (1) The representative representative of the case is the picture of (1A). (b) The symbol of the representative figure is briefly described as follows: 1 microporous fluid path element 2 fluid application end 3 outflow end 5 pad 6 contact area 7 pad 8 contact area 9 first sealing element 10 substrate 11 second sealing element 12 Receiving element 13 fluid receiving area 14 air insulating element 15 gas chamber 16 discharge end 20 application end 21 fluid circuit 22 covering element, fluid circuit 8. If there is a chemical formula in this case, please reveal the chemical formula that best shows the characteristics of the invention.